US20110307018A1 - Adaptive spinal rod and methods for stabilization of the spine - Google Patents

Adaptive spinal rod and methods for stabilization of the spine Download PDF

Info

Publication number
US20110307018A1
US20110307018A1 US13014878 US201113014878A US2011307018A1 US 20110307018 A1 US20110307018 A1 US 20110307018A1 US 13014878 US13014878 US 13014878 US 201113014878 A US201113014878 A US 201113014878A US 2011307018 A1 US2011307018 A1 US 2011307018A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
ball
rod
spinal rod
bone anchor
adaptive
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US13014878
Inventor
James F. Zucherman
Charles J. Winslow
Ken Y. Hsu
Steven T. Mitchell
John J. Flynn
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Spartek Medical Inc
Original Assignee
Spartek Medical Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/70Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
    • A61B17/7001Screws or hooks combined with longitudinal elements which do not contact vertebrae
    • A61B17/7002Longitudinal elements, e.g. rods
    • A61B17/7004Longitudinal elements, e.g. rods with a cross-section which varies along its length
    • A61B17/7007Parts of the longitudinal elements, e.g. their ends, being specially adapted to fit around the screw or hook heads
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/70Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
    • A61B17/7001Screws or hooks combined with longitudinal elements which do not contact vertebrae
    • A61B17/7041Screws or hooks combined with longitudinal elements which do not contact vertebrae with single longitudinal rod offset laterally from single row of screws or hooks
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/70Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
    • A61B17/7074Tools specially adapted for spinal fixation operations other than for bone removal or filler handling
    • A61B17/7076Tools specially adapted for spinal fixation operations other than for bone removal or filler handling for driving, positioning or assembling spinal clamps or bone anchors specially adapted for spinal fixation
    • A61B17/7082Tools specially adapted for spinal fixation operations other than for bone removal or filler handling for driving, positioning or assembling spinal clamps or bone anchors specially adapted for spinal fixation for driving, i.e. rotating, screws or screw parts specially adapted for spinal fixation, e.g. for driving polyaxial or tulip-headed screws
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/56Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws, setting implements or the like
    • A61B17/68Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/70Spinal positioners or stabilisers ; Bone stabilisers comprising fluid filler in an implant
    • A61B17/7001Screws or hooks combined with longitudinal elements which do not contact vertebrae
    • A61B17/7002Longitudinal elements, e.g. rods
    • A61B17/7011Longitudinal element being non-straight, e.g. curved, angled or branched

Abstract

An adaptive spinal rod is provided for connecting levels of an adaptive stabilization system to support the spine while providing for the preservation of spinal motion. Embodiments of the adaptive stabilization rod include a ball having an anchor system, a deflection system, a vertical rod system and a connection system. The deflection system provides adaptive stabilization and load-sharing. The adaptive spinal rod connects different levels of the construct in a multilevel construct. The adaptive spinal rod cooperates with the deflection system to further reduce stress exerted upon the bone anchors and spinal anatomy.

Description

    CLAIM TO PRIORITY
  • This patent application claims priority to the following patents and patent applications:
  • U.S. Provisional Patent Application No. 61/353,508, filed Jun. 10, 2010, entitled “ADAPTIVE SPINAL ROD AND METHODS FOR STABILIZATION OF THE SPINE” (Attorney Docket No. SPART-01058US0); and
  • U.S. Provisional Patent Application No. 61/435,961, filed Jan. 25, 2011, entitled “ADAPTIVE SPINAL ROD AND METHODS FOR STABILIZATION OF THE SPINE” (Attorney Docket No. SPART-01058US1).
  • All of the afore-mentioned patent applications are incorporated herein by reference in their entireties.
  • CROSS-REFERENCES TO RELATED APPLICATIONS
  • This application is related to all of the afore-mentioned patent applications. This application is also related to all of the following applications including:
  • U.S. patent application Ser. No. 13/014,868, filed Jan. 27, 2011, entitled “ADAPTIVE SPINAL ROD AND METHODS FOR STABILIZATION OF THE SPINE” (Attorney Docket No. SPART-01058US2); and
  • U.S. patent application Ser. No. 13/______, filed Jan. 27, 2011, entitled “ADAPTIVE SPINAL ROD AND METHODS FOR STABILIZATION OF THE SPINE” (Attorney Docket No. SPART-01058US4).
  • All of the afore-mentioned patent applications are incorporated herein by reference in their entireties.
  • BACKGROUND OF INVENTION
  • Back pain is a significant clinical problem and the costs to treat it, both surgical and medical, are estimated to be over $2 billion per year. One method for treating a broad range of degenerative spinal disorders is spinal fusion. Implantable medical devices designed to fuse vertebrae of the spine to treat have developed rapidly over the last decade. However, spinal fusion has several disadvantages including reduced range of motion and accelerated degenerative changes adjacent the fused vertebrae.
  • Alternative devices and treatments have been developed for treating degenerative spinal disorders while preserving motion. These devices and treatments offer the possibility of treating degenerative spinal disorders without the disadvantages of spinal fusion. However, current devices and treatments suffer from disadvantages e.g., complicated implantation procedures; lack of flexibility to conform to diverse patient anatomy; the need to remove tissue and bone for implantation; increased stress on spinal anatomy; insecure anchor systems; poor durability, and poor revision options. Consequently, there is a need for new and improved devices and methods for treating degenerative spinal disorders while preserving motion.
  • SUMMARY OF INVENTION
  • The present invention includes a spinal implant system and methods that can dynamically stabilize the spine while providing for the preservation of spinal motion. Embodiments of the invention provide an adaptive spinal stabilization system which includes: versatile components, adaptive stabilization assemblies, and methods of implantation. An aspect of embodiments of the invention is the ability to stabilize two, three and/or more levels of the spine by the selection of appropriate components of embodiments of the invention for implantation in a patient. Another aspect of embodiments of the invention is the ability to accommodate particular anatomy of the patient by providing a system of versatile components which may be customized to the anatomy and needs of a particular patient and procedure. Another aspect of the invention is to facilitate the process of implantation and minimize disruption of tissues during implantation.
  • Thus, the present invention provides new and improved systems, devices and methods for treating degenerative spinal disorders by providing and implanting an adaptive spinal stabilization assembly which supports the spine while preserving motion. These and other objects, features and advantages of the invention will be apparent from the drawings and detailed description which follow.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1A is an exploded view of an adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 1B is a perspective view of an assembled adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 1C is a perspective view of a bone anchor for adapted for use with the adaptive spinal rod of FIGS. 1A, and 1B according to an embodiment of the present invention.
  • FIG. 1D is a perspective view of a spinal prosthesis including the adaptive spinal rod of FIGS. 1A, and 1B and bone anchor of FIG. 1C according to an embodiment of the present invention.
  • FIG. 1E is a saggital section of the spinal prosthesis of FIG. 1D.
  • FIG. 1F is a transverse section of the spinal prosthesis of FIG. 1D.
  • FIG. 1G is a dorsal section of the spinal prosthesis of FIG. 1D.
  • FIG. 1H is a perspective view of a two-level spinal prosthesis including the adaptive spinal rod of FIGS. 1A, and 1B and bone anchor of FIG. 1C according to an embodiment of the present invention.
  • FIG. 2A is an exploded view of an adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 2B is a perspective view of a bone anchor suitable for use with the adaptive spinal rod of FIG. 2A according to an embodiment of the present invention.
  • FIG. 2C is a perspective view of an assembly including the bone anchor of FIG. 2B and the adaptive spinal rod of FIG. 2A according to an embodiment of the present invention.
  • FIG. 2D is a saggital section of the assembly of FIG. 1C as implanted.
  • FIG. 2E is a transverse section of the spinal prosthesis of FIG. 1C as implanted.
  • FIG. 2F is a dorsal section of the spinal prosthesis of FIG. 1C as implanted.
  • FIG. 3A is an exploded view of a first segment of a two-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 3B is an enlarged view illustrating features of a ball for use in a sliding ball-joint according to an embodiment of the invention.
  • FIG. 3C is a perspective view of the first segment of a two-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 3D is a perspective view of the second segment of a two-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 3E is a perspective view of a bone anchor for use with the two-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 3F is a perspective view of a spinal prosthesis including the two-level adaptive spinal rod of FIGS. 1A, and 1B and bone anchor of FIG. 1C according to an embodiment of the present invention.
  • FIG. 3G is a partial sectional view illustrating motion limiting features of adaptive spinal rod according to embodiments of the present invention.
  • FIG. 3H is a perspective view of an alternative single-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 4A is an exploded view of a first segment of a two-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 4B is an exploded view of a second segment of a two-level adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 4C is a perspective view of an adaptive spinal rod including the components of FIGS. 4A and 4B according to an embodiment of the present invention.
  • FIG. 4D is a perspective view of an adaptive spinal prosthesis including the two-level adaptive spinal rod of FIGS. 4A-4C according to an embodiment of the present invention.
  • FIG. 5A is an exploded view of a two-level adaptive spinal rod according to an alternative embodiment of the present invention.
  • FIG. 5B is a perspective view of an adaptive spinal rod including the components of FIG. 5A according to an embodiment of the present invention.
  • FIG. 5C is a saggital section of a two-level adaptive spinal prosthesis incorporating the adaptive spinal rod of FIG. 5B.
  • FIG. 5D is a transverse section of a two-level adaptive spinal prosthesis incorporating the adaptive spinal rod of FIG. 5B.
  • FIG. 5E is a dorsal section of a two-level adaptive spinal prosthesis incorporating the adaptive spinal rod of FIG. 5B.
  • FIG. 5F shows a spacer which is, in some embodiments, incorporated into the two-level adaptive spinal rod of FIG. 5B.
  • FIG. 5G is a perspective view of an adaptive spinal rod including the components of FIGS. 5A through 5E according to an alternative embodiment of the present invention.
  • FIG. 5H is a dorsal section of a two-level adaptive spinal prosthesis incorporating the adaptive spinal rod of FIG. 5G.
  • FIG. 6A is a view of an adaptive spinal rod according to an alternative embodiment of the present invention.
  • FIG. 6B is a view of a bone anchor for use in a two-level adaptive stabilization system according to an alternative embodiment of the present invention.
  • FIG. 6C is an exploded view of a polyaxial connector for use in a two-level adaptive stabilization system according to an alternative embodiment of the present invention.
  • FIG. 6D is an alternative view of a component of the connector of FIG. 6C.
  • FIGS. 6E and 6F are views illustrating the clamping action of the polyaxial connector of FIG. 6C.
  • FIG. 6G is a perspective view illustrating a two-level adaptive spinal prosthesis utilizing the components of FIGS. 6A-6D.
  • FIG. 7A is an exploded view of an adaptive spinal rod according to an embodiment of the present invention.
  • FIG. 7B is a perspective view of the adaptive spinal rod of FIG. 7A.
  • FIG. 7C is a partial sectional view of the adaptive spinal rod of FIG. 7A.
  • FIG. 8A shows a perspective view of an implantation tool for an adaptive bone anchor according to an embodiment of the invention.
  • FIGS. 8B and 8C show detailed sectional views of the head of the implantation tool of FIG. 8A in relation to the bone anchor.
  • FIG. 8D is a transverse view of the lumbar spine illustrating use of the implantation tool of FIG. 8A to implant a bone anchor in the pedicles of a lumbar vertebra according to an embodiment of the invention.
  • FIG. 9A shows a perspective view of an attachment tool for securing an adaptive spinal rod to a bone anchor according to an embodiment of the invention.
  • FIG. 9B shows a detailed view of the head of the attachment tool of FIG. 9A.
  • FIGS. 9C and 9D show detailed sectional views of the head of the attachment tool of FIG. 9A in relation to an adaptive spinal rod and bone anchor.
  • FIG. 9E-9H are a lateral views of the lumbar spine illustrating steps to secure an adaptive spinal rod to a bone anchor using the attachment tool of FIG. 9A according to an embodiment of the invention.
  • FIG. 10A is a view of an adaptive spinal rod according to an alternative embodiment of the present invention.
  • FIG. 10B is a view of a bone anchor for use in a two-level adaptive stabilization system according to an alternative embodiment of the present invention.
  • FIG. 10C is an exploded view of a polyaxial connector for use in a two-level adaptive stabilization system according to an alternative embodiment of the present invention.
  • FIG. 10D is an alternative view of a component of the connector of FIG. 10C.
  • FIGS. 10E and 10F are views illustrating the clamping action of the polyaxial connector of FIG. 10C.
  • FIG. 10G is a perspective view illustrating a two-level adaptive spinal prosthesis utilizing the components of FIGS. 10A-10D.
  • FIG. 11A is an exploded view of an adaptive spinal rod according to an alternative embodiment of the present invention.
  • FIG. 11B is a perspective view of the adaptive spinal rod of FIG. 11A as assembled.
  • FIG. 11C is a perspective view of a bone anchor adapted for use with the adaptive spinal rod of FIGS. 11A, and 11B according to an embodiment of the present invention.
  • FIG. 11D is a perspective view of a spinal prosthesis including the adaptive spinal rod of FIGS. 11A and 11B and bone anchor of FIG. 11C.
  • FIG. 11E is a saggital section of the spinal prosthesis of FIG. 11D.
  • FIG. 11F is a transverse section of the spinal prosthesis of FIG. 11D.
  • FIG. 11G is a dorsal section of the spinal prosthesis of FIG. 11D.
  • FIG. 11H is a dorsal section of the spinal prosthesis of FIG. 11D.
  • FIG. 11I is a composite view of FIGS. 11G and 11H.
  • FIG. 12A is an exploded view of an adaptive spinal rod according to an alternative embodiment of the present invention.
  • FIG. 12B is a plane view of the adaptive spinal rod of FIG. 11A as assembled.
  • FIG. 12C is a perspective view of the adaptive spinal rod of FIG. 11A as assembled.
  • In the figures and detail description that follows common reference numerals are used to indicate like elements throughout the drawings and detailed description; therefore, reference numerals used in a drawing may or may not be referenced in the detailed description specific to such drawing if the associated element is referenced and described elsewhere. Elements having identical reference numbers differing only by a terminal reference letter are related and/or identical—the description of the structure and/or function of each such element should be considered with respect to all such elements to the extent differences between the elements are not specified. The first digit in a three digit reference numeral indicates the series of figures in which the referenced item first appears. Likewise the first two digits in a four digit reference numeral.
  • The terms “vertical” and “horizontal” are used throughout the detailed description to describe general orientation of structures relative to the spine of a human patient that is standing. This application also uses the terms proximal and distal in the conventional manner when describing the components of the spinal implant system. Thus, proximal refers to the end or side of a device or component closest to the hand operating the device, whereas distal refers to the end or side of a device furthest from the hand operating the device. For example, the tip of a bone screw that enters a bone would conventionally be called the distal end (it is furthest from the surgeon) while the head of the screw would be termed the proximal end (it is closest to the surgeon).
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • The present invention includes a versatile spinal implant system and methods which can stabilize the spine while providing for the preservation of spinal motion. Alternative embodiments can be used for spinal fusion. An aspect of the invention is stabilizing the spine while restoring and/or preserving the natural motion of the spine including the quality of motion as well as the range of motion. Still, another aspect of the invention is providing for load sharing and stabilization of the spine while preserving motion. Another aspect of embodiments of the invention is the ability to stabilize two, three and/or more levels of the spine by the selection of appropriate components for implantation in a patient. Another aspect of the invention is the ability to provide for higher stiffness and fusion at one level or to one portion of the spine while allowing for lower stiffness and adaptive stabilization at another adjacent level or to another portion of the spine. Embodiments of the invention allow for fused levels to be placed next to dynamically stabilized levels. Such embodiments of the invention enable vertebral levels adjacent to fusion levels to be shielded by providing a transition from a rigid fusion level to a dynamically stable, motion preserved, and more mobile level. Alternative embodiments can be utilized in spinal fusion procedures.
  • Embodiments of the present invention provide for assembly of an adaptive spinal prosthesis which supports the spine while providing for the preservation of spinal motion. Another aspect of the invention is to provide an adaptable modular system which can be utilized to create an adaptive spinal prosthesis customized to the needs of the patient. The adaptive stabilization system includes bone anchors and adaptive spinal rods. The bone anchors secure the adaptive spinal stabilization system to the spinal anatomy. The adaptive spinal rods provide adaptive stabilization by contributing for load sharing and stabilization of the spine while preserving motion. Embodiments of the invention include surgical kits, surgical methods, constructs, and prostheses including: an adaptive spinal rod; a bone screw specifically designed for use with an adaptive spinal rod; a bone anchor in combination with an adaptive spinal rod; a plurality of bone anchors in combination with an adaptive spinal rod; a plurality of bone anchors in combinations with a plurality of adaptive spinal rods.
  • Adaptive Stabilization System
  • FIGS. 1A-1G are views of an adaptive stabilization system including an adaptive spinal rod according to an embodiment of the present invention. FIG. 1A is an exploded view showing the components of an adaptive spinal rod. FIG. 1B is a perspective view of the assembled adaptive spinal rod. FIG. 1C shows a perspective view of a bone anchor suitable for mounting the adaptive spinal rod to a vertebra. FIG. 1D shows a spinal prosthesis assembly including the adaptive spinal rod, a bone anchor and a conventional pedicle screw. FIGS. 1E, 1F and 1G are sectional views illustrating the kinematics of the bone anchor relative to the adaptive spinal rod.
  • Referring first to FIG. 1A, which is an exploded view of the components of an adaptive spinal rod 100. Adaptive spinal rod 100 has three components: rod 110 including housing 120, ball 130 and cap 140. Rod 110 is connected at one end to housing 120. Rod 110 is preferably similar in size, shape and material to standard spinal rods. Rod 110 is preferably adapted for mounting to a standard pedicle screw or polyaxial screw (not shown). Rod 110 is, in preferred embodiments, a cylinder of about 5 mm to 6.5 mm in diameter and from 35 mm to 100 mm in length. Housing 120 is preferably in the form of a flattened disc. Housing 120 has a slot 122 passing there through. Slot 122 is shaped to receive ball 130 from open side 124 however, the closed side 126 of slot 122 is too small for ball 130 to pass. Slot 122 and thus linear race 102 can be elongated to allow ball 130 to slide in slot 122 as explained below. It is to be understood that linear race 102, in addition to being elongated such that ball 130 can move linearly along the direction of the longitudinal axis of rod 110, can be oval and/or elliptical shaped and/or rectangular with rounded corners and/or race-track shaped such that ball 130 can move linearly in any direction. Further, slot 122 and thus linear race 102 can be an enlarged sphere shaped such that ball 130 can move in any linear direction relative to the sphere as well as pivoting and rotating relative to linear race 102. Open side 124 of slot 122 is shaped to receive cap 140. Closed side 126 of slot 122 has a curved surface 128 adapted to engage ball 130. In one embodiment curved surface 128 has the same radius of curvature as ball 130. Cap 140 can be force fit or welded in place to the housing 120 to hold ball 130 in place. In preferred embodiments, rod 110 and housing 120 are made in one piece from titanium or titanium alloy.
  • Ball 130 is in the form of a sphere truncated on two opposing sides 132, 134. An aperture 136 passes through ball 130 from side 132 to side 134. As shown in FIG. 1A, one end of aperture 136 is provided with tool engagement features 138 (a hexagonal depression is shown) which allow ball 130 to be engaged and turned by a tool. The other end of aperture 136 has a threaded wall 139 adapted to allow ball 130 to be secured to a threaded screw (not shown). Thus, ball 130 is adapted to be secured to a threaded shaft (not shown) without using a separate nut. In alternative embodiments aperture 136 is not provided with tool engagement features 138 or threaded wall 139 and is adapted to be secured to a threaded shaft (not shown) with a separate threaded nut/fastener (not shown).
  • Cap 140 is adapted to fit within slot 122 of housing 120. Cap 140 has a cap slot 142 therethrough. The open side 144 of slot 142 is configured to admit a portion of ball 130. The closed side 146 of slot 142 is too small for ball 130 to pass. The interior of slot 142 has a curved surface 148 adapted to engage ball 130. In one embodiment curved surface 148 has the same radius of curvature as ball 130.
  • During assembly, ball 130 is placed into slot 122 of housing 120. Cap 140 is then secured into slot 122 of housing 120 trapping or containing ball 130 between cap 140 and housing 120. FIG. 1B shows a fully assembled adaptive spinal rod 100 in which ball 130 is positioned between cap 140 and housing 120. Slot 122 of housing 120 and slot 142 of cap 140 cooperate to from a linear race 102 in which ball 130 is trapped or contained. Although ball 130 is trapped or contained within linear race 102, ball 130 can pivot and rotate within linear race 102 as shown by arrows 160, 162. Ball 130 can also slide a small distance along linear race 102 as shown by arrow 164. As shown in FIG. 1B, aperture 136 of ball 130 is accessible after ball 130 has been secured between cap 140 and housing 120. In adaptive spinal rod 100 as assembled, aperture 136 of ball 130 is accessible and configured for mounting adaptive spinal rod 100 to a threaded shaft of a pedicle screw as shown, for example in FIG. 1C. In combination, the surface of ball 130, and the linear race 102 form a sliding ball-joint 101.
  • FIG. 1C shows a bone anchor 150 configured for attachment of adaptive spinal rod 100 to a vertebra. As shown in FIG. 1C, bone anchor 150 includes a threaded shaft 152 at the distal end. Threaded shaft 152 is sized and configured for engaging a vertebra. In preferred embodiments threaded shaft 152 is sized and configured for implantation in the pedicle of a vertebra. Attached to threaded shaft 152 is head 154. Head 154 includes surface features 155 which permit head to be engaged by a tool to rotate head 154 and threaded shaft 152 and drive bone anchor 150 into a desired implant location. Protruding proximally from head 154 is a mount 156. Mount 156 has a threaded exterior surface 157 to which ball 130 of FIGS. 1A and 1B can be mounted. Protruding proximally of mount 156 is key 158. Key 158 is shaped such that the key 158 can be engaged by a driver for implanting bone anchor 150 and/or attaching ball 130. For example, key 158 has, in some embodiments, a hexagonal or octagonal cross-section. At the base of key 158 is a groove 159. Groove 159 reduces the cross-section of material such that the key 158 is designed to breakaway when a predetermined amount of torque is applied to key 158. The breakaway torque is determined by the shape of groove 159 and the remaining cross-section of material.
  • FIG. 1D shows the relationship between a spinal prosthesis 104 and a spine 190. Spinal prosthesis 104 includes, in this embodiment: adaptive spinal rod 100 of FIGS. 1A and 1B; bone anchor 150 of FIG. 1C; and a conventional spinal screw 170. Spinal screw 170 is, in some embodiments, a polyaxial pedicle screw. As shown in FIG. 1D, adaptive spinal rod 100 is secured at one end to the bone anchor 150 of FIG. 1C and at the other end to conventional spinal screw 170. Ball 130, trapped or contained within linear race 102, has been secured to mount 156 of bone anchor 150. Breakaway key 158 is broken away from mount 156 during implantation and removed from the patient. Rod 110 has been secured into a slot 172 in a head 174 of spinal screw 170 by a set screw 173. Set screw 173 secures rod 110 in a fixed position relative to head 174 and also, in some embodiments, locks the position of head 174 relative to the threaded screw shaft 176 of spinal screw 170.
  • In spinal prosthesis 104, rod 110 and housing 120 of adaptive spinal rod 100 are secured in a fixed position, as shown in FIG. 1D, relative to spinal screw 170. However, ball 130 is still able pivot rotate and slide in linear race 102 relative to housing 120 of adaptive spinal rod 100 (see FIG. 1C). Consequently, with bone anchor 150 secured to adaptive spinal rod 100 through ball 130, bone anchor 150 is still able to slide, pivot and rotate relative to rod 110 and spinal screw 170. (See FIGS. 1E, 1F and 1G).
  • Referring again FIG. 1D which shows the relationship between a spinal prosthesis 105 and a spine 190. Bone anchor 150 is implanted in a vertebra 192 a passing through pedicle 194 a into spinal body 196 a. Spinal screw 170 is implanted in a vertebra 192 b passing through a pedicle 194 b into spinal body 196 b. A second spinal screw 170 is implanted in a vertebra 192 c passing through a pedicle 194 c into spinal body 196 c. Spinal screws 170 and rod 110 b hold vertebrae 192 b and 192 c in fixed relationship. This embodiment of a spinal prosthesis is suitable for use for example, where vertebrae 192 b and 192 c are to be fused together. As shown in FIG. 1D, where bone anchor 150 and rod 110 b provides load-sharing and permits a controlled range of motion between the adjacent vertebrae 192 a, 192 b. Thereby stabilizing a level of the spine 190 while restoring and/or preserving some natural motion of the vertebrae 192 a, 192 b at that level. This configuration can, in some embodiments, be utilized to prevent adjacent segment deterioration by supporting a spinal motion segment adjacent a spinal fusion.
  • FIGS. 1E, 1F and 1G show the kinematics of bone anchor 150 relative to rod 110 of adaptive spinal rod 100 when assembled as part of an adaptive spinal prosthesis. FIG. 1E shows a section through bone anchor 150 and adaptive spinal rod 100 in a substantially saggital plane. FIG. 1F shows a section through bone anchor 150 and adaptive spinal rod 100 in a transverse plane. FIG. 1G shows a section through bone anchor 150 and adaptive spinal rod 100 in a substantially dorsal plane through the middle of the housing 120.
  • Referring first to FIG. 1E which shows a section through bone anchor 150 and adaptive spinal rod 100 in a substantially saggital plane (vertical and including the longitudinal axis of bone anchor 150). The dotted outlines of bone anchor 150 illustrate a range of possible movements of bone anchor 150 in the saggital plane. As shown in FIG. 1E, ball 130 is trapped or contained between cap 140 and housing 120 to form a sliding ball-joint 101. Ball 130 can move within limits imposed by contact with housing 120 and cap 140. Bone anchor 150 thus can pivot and translate relative to rod 110 in the plane shown.
  • In the saggital plane shown in FIG. 1E, the sliding ball-joint 101 allows bone anchor 150 a limited vertical range of movement (shown by arrow 180). The translation is limited by contact between ball 130, cap 140 and, in some embodiments, bone anchor 150. The desired range of vertical motion 180, and thus the dimensions of sliding ball-joint 101, are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of vertical movement is limited to less than 5 mm. In preferred embodiments, the range of horizontal and vertical movement is limited to less than 1.5 mm. The length of linear race 102 (along the long axis of rod 110) controls the vertical range of movement.
  • In the saggital plane shown in FIG. 1E, the sliding ball-joint 101 also allows bone anchor 150 a limited angular range of movement which corresponds to spinal flexion/extension (shown by arrow 182). The range of angular movement translation is limited by contact between ball 130, housing 120 and cap 140 and, in some embodiments, mount 156. The desired range of angular motion 182, and thus the shape of ball 130, housing 120 and cap 140 and, in some embodiments, mount 156 are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of angular movement in the saggital plane is limited to less than 15 degrees. In preferred embodiments, the range of angular movement in the saggital plane is limited to less than 15 degrees.
  • In the transverse plane shown in FIG. 1F, the sliding ball-joint 101 allows bone anchor 150 a limited angular range of movement which corresponds to spinal rotation (shown by arrow 184). The range of angular movement is limited by contact between ball 130, housing 120 and cap 140 and, in some embodiments, mount 156. The desired range of angular motion 184, and thus the shape of ball 130, housing 120 and cap 140 and, in some embodiments, mount 156 are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of angular movement in the transverse plane is limited to less than 10 degrees. In preferred embodiments, the range of angular movement in the transverse plane is limited to less than 15 degrees. The range of angular movement in the transverse plane can be different than the range in the vertical plane. The range of angular movement in the transverse plane need not be the same as the range of angular movement in the saggital plane (see FIG. 1E).
  • Referring next to FIG. 1G which shows a section through bone anchor 150 and adaptive spinal rod 100 in a substantially dorsal plane (vertical and perpendicular to the longitudinal axis of bone anchor 150). As shown in FIG. 1G, ball 130 is trapped or contained in linear race 102 formed by cap 140 in conjunction with housing 120. Ball 130 can move within linear race 102. Bone anchor 150 is oriented either directly into or directly out of the page in this transverse view through housing 120. Bone anchor 150 is mounted to ball 130 and thus can move relative to rod 110 with one angular degree of freedom and one linear degree shown in this view.
  • In the dorsal plane shown in FIG. 1G, sliding ball-joint 101 allows bone anchor 150 the limited vertical range of movement 180 as described above. Rotation of ball 130 within sliding ball-joint 101 is unrestricted, allowing bone anchor 150 to rotate freely (360+ degrees) as shown by arrow 186 which corresponds to lateral spinal twisting. The bone anchor 150 rotates freely around the longitudinal axis of the bone anchor. The range of rotation 186 is not limited in this embodiment. However features to limit such rotation could be designed into one or more of bone anchor 150, ball 130, cap 140, and housing 120. The desired range of rotation 186, can be selected, if necessary or desirable, based upon the anatomical and functional needs of a patient.
  • FIGS. 2A-2F are views of an alternative adaptive stabilization system including an adaptive spinal rod according to an embodiment of the present invention. FIG. 2A is an exploded view showing the components of an adaptive spinal rod. FIG. 2B shows a perspective view of a bone anchor suitable for mounting the adaptive spinal rod to a vertebra. FIG. 2C is a perspective view of the assembled adaptive spinal rod and bone anchor. FIGS. 2D 2E and 2F are sectional views illustrating the kinematics of the bone anchor relative to the adaptive spinal rod.
  • Referring first to FIG. 2A, which is an exploded view of the components of an adaptive spinal rod 200. Adaptive spinal rod 200 has three components: rod 210 including housing 220, half-ball 230 and half-ball retainer 240. Rod 210 is connected at one end to housing 220. Rod 210 is similar in size, shape and material to standard spinal rods. Rod 210 is adapted for mounting to a standard pedicle screw or polyaxial screw (not shown). Rod 210 is in preferred embodiments, preferably a cylinder of about 5 mm to 6.5 mm in diameter and from 35 mm to 200 mm in length. Housing 220 is preferably in the form of a flattened disc.
  • Housing 220 has a slot 222 passing there through. Slot 222 has convex walls and slot 222 is thus wider at the openings of slot 222 than in the interior of slot 222. Thus half-ball 230 can partially enter one side of slot 222, but cannot pass entirely through slot 222. Likewise half-ball retainer 240 can partially enter one side of slot 222, but cannot pass entirely through slot 222. In preferred embodiments, rod 210 and housing 220 are made in one piece from titanium or titanium alloy.
  • Half-ball 230 is in the form of a hemisphere. An aperture 236 passes through half-ball 230 from domed side 232 to flat side 234. As shown in FIG. 2A, aperture 236 is, in some embodiments, provided with tool engagement features which allow ball 230 to engage a mounting post (for example threads or a hexagonal section.
  • Hall-ball retainer 240 in the form of a hemisphere with a nut extending from the flat surface. An aperture 246 passes through half-ball retainer 240 from domed side 242 to flat side 244. As shown in FIG. 2A, part of the surface of half-ball retainer 240 is provided with tool engagement features 248 (splines are shown) which allow half-ball retainer 240 to be engaged and turned by a tool. The interior of aperture 246 has a threaded wall 249 adapted to allow half-ball retainer 240 to be secured to a threaded screw (bone anchor 250 of FIG. 2B). Thus, half-ball retainer 240 is adapted to be secured to a threaded shaft (thread 258 of FIG. 2B) without using a separate nut. In alternative embodiments half-ball retainer 240 can be provided in two pieces including for example a half-ball component and a standard nut.
  • FIG. 2B, shows a bone anchor 250 configured for attachment of adaptive spinal rod 200 to a vertebra. As shown in FIG. 2B, bone anchor 250 includes a threaded shaft 252 at the distal end. Threaded shaft is sized and configured for engaging a vertebra. In preferred embodiments threaded shaft 252 is sized and configured for implantation in the pedicle of a vertebra. At the proximal end of threaded shaft 252 is a head 254 which has, in some embodiments, tool engagement features (not shown). Protruding proximally from head 254 is mount 256. Mount 256 has a cylindrical exterior surface 257 to which ball 230 of FIG. 2A can be secured. Protruding proximally of mount 256 is threaded shaft 258. Threaded shaft 258 is adapted for attaching half-ball retainer 240. In the proximal end of threaded shaft 258 is an aperture 259. Aperture 259 is shaped such that aperture 259 can be engaged by a driver for implanting bone anchor 250 and/or attaching half-ball retainer 240. For example, aperture 259 has, in some embodiments, a hexagonal or octagonal cross-section. In alternative embodiments aperture 259 is replaced with a breakaway key such as key 158 of FIG. 1C. In combination, the domed surfaces of half-ball 230, and half-ball retainer 240 and the convex surface of slot 222 form an alternative sliding ball-joint 201.
  • FIG. 2C is a perspective view of adaptive spinal rod 200 in combination with bone anchor 250. As shown in FIG. 2C, half-ball 230 is placed over mount 256 (FIG. 2B). Slot 222 is then placed over mount 256 (FIG. 2B). A portion of the domed surface 232 of half-ball 230 enters slot 222. Finally half-ball retainer 240 is secured the threaded shaft 258 (FIG. 2B). A portion of the domed surface 242 of half-ball retainer 240 enters slot 222. Half-ball 230 and half-ball retainer 240 may, in some but not all embodiments, contact one another inside slot 222. Upon assembly slot 222 performs as race 202 for half-ball 230 and half-ball retainer 240. Thus, bone anchor 250 can slide, pivot and rotate relative to housing 220 and rod 210 of adaptive spinal rod 200. It is to be understood that slot 222 and thus race 202 can be linear and also can be configured in accordance with the various configurations of slot 122 and linear race 102 shown in the embodiments of FIGS. 1A-1H.
  • In embodiments, adaptive spinal rod 200 and bone anchor 250 can be used in place of adaptive spinal rod 100 and bone anchor 150 to create a spinal prosthesis similar to spinal prosthesis 104 of FIG. 1D. In such a spinal prosthesis, rod 210 and housing 220 of adaptive spinal rod 200 are secured in a fixed position, by a pedicle screw. However, slot 222 is still able pivot rotate and slide relative to half-ball 230 and half-ball retainer 240. Consequently, with bone anchor 250 secured to adaptive spinal rod 200 by sliding ball-joint 201 is still able to slide, pivot and rotate relative to rod 210. (See FIGS. 2D, 2E and 2F). Adaptive spinal rod 200 is configured to provide load-sharing and permit a controlled range of motion between adjacent vertebrae. Thereby, stabilizing a level of the spine while restoring and/or preserving some natural motion of the vertebrae at that level.
  • FIGS. 2D, 2E and 2F show the kinematics of bone anchor 250 relative to rod 210 of adaptive spinal rod 200 when assembled as part of a spinal prosthesis. FIG. 2D shows a section through bone anchor 250 and adaptive spinal rod 200 in a substantially saggital plane. FIG. 2E shows a section through bone anchor 250 and adaptive spinal rod 200 in a transverse plane. FIG. 2F shows a section through bone anchor 250 and adaptive spinal rod 200 in a substantially dorsal plane through the middle of the housing 220.
  • Referring first to FIG. 2D which shows a section through bone anchor 250 and adaptive spinal rod 200 in a substantially saggital plane (vertical and including the longitudinal axis of bone anchor 250). The dotted outlines of bone anchor 250 illustrate a range of possible movements of bone anchor 250 in the saggital plane. As shown in FIG. 2D, half-ball 230 and half-ball retainer 240 trap or contain the convex surface of slot 222. Slot 222 can move within limits imposed by contact with half-ball 230 and half-ball retainer 240 (and, in some embodiments, mount 256. Bone anchor 250 thus can pivot and translate relative to rod 210 in the plane shown.
  • In the saggital plane shown in FIG. 2D, the sliding ball-joint 201 allows bone anchor 250 a limited vertical range of movement (shown by arrow 280) and a limited horizontal range of movement 288. The translation is limited by contact between slot 222 and half-ball 230, half-ball retainer 240 and, in some embodiments, mount 256. The desired range of vertical motion 280 and horizontal motion 288, and thus the dimensions of sliding ball-joint 201, are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of horizontal and vertical movement is limited to less than 5 mm. In preferred embodiments, the range of horizontal and vertical movement is limited to less than 2.5 mm. The horizontal and vertical range of movement need not be the same. The width of slot 222 (perpendicular to the long axis of rod 210) controls the horizontal range of movement while the length of slot 222 (along the long axis of rod 210) controls the vertical range of movement.
  • In the saggital plane shown in FIG. 2D, the sliding ball-joint 201 also allows bone anchor 250 a limited angular range of movement which corresponds to spinal flexion/extension (shown by arrow 282). The range of angular movement translation is limited by contact between slot 222 and half-ball 230, half-ball retainer 240 and, in some embodiments, mount 256. The desired range of angular motion 282, and thus the shape of slot 222 and half-ball 230, half-ball retainer 240 and, in some embodiments, mount 256 are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of angular movement in the saggital plane is limited to less than 20 degrees. In preferred embodiments, the range of angular movement in the saggital plane is limited to less than 20 degrees.
  • In the transverse plane shown in FIG. 2E, the sliding ball-joint 201 allows bone anchor 250 a limited horizontal range of movement (shown by arrow 289) and a limited horizontal range of movement 288. The translation is limited by contact between slot 222 and half-ball 230, half-ball retainer 240 and, in some embodiments, mount 256. The desired range of horizontal motion 288 and horizontal motion 289, and thus the dimensions of sliding ball-joint 201, are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of horizontal and vertical movement is limited to less than 5 mm. In preferred embodiments, the range of horizontal and vertical movement is limited to less than 2.5 mm. The horizontal ranges of movement need not be the same an can be adjusted by changing, dimensions of the sliding ball-joint 201, including, for example: the curvature of the slot 222, half-ball 230, and half-ball retainer 240, the width of slot 222, and gap between half-ball 230, and half-ball retainer 240.
  • In the transverse plane shown in FIG. 2E, the sliding ball-joint 201 also allows bone anchor 250 a limited angular range of movement which corresponds to spinal rotation (shown by arrow 284). The range of angular movement is limited by contact between slot 222 and half-ball 230, half-ball retainer 240 and, in some embodiments, mount 256. The desired range of angular motion 284, and thus the shape of slot 222 and half-ball 230, half-ball retainer 240 and, in some embodiments, mount 256 are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of angular movement in the transverse plane is limited to less than 20 degrees. In preferred embodiments, the range of angular movement in the transverse plane is limited to less than 20 degrees. The range of angular movement in the transverse plane can be different than the range in the vertical plane.
  • Referring next to FIG. 2F which shows a section through bone anchor 250 and adaptive spinal rod 200 in a substantially dorsal plane (vertical and perpendicular to the longitudinal axis of bone anchor 250). As shown in FIG. 2F, mount 256 is trapped or contained in linear race 202 formed slot 222 and half-ball 230, half-ball retainer 240. Mount 256 can move within race 202. Bone anchor 150 can thus move relative to rod 210 with one angular degree of freedom and one linear degree shown in this view. Bone anchor 250 is oriented either directly into or directly out of the page in this transverse view through housing 220.
  • In the dorsal plane shown in FIG. 2F, sliding ball-joint 201 allows bone anchor 250 the limited horizontal and vertical range of movement (shown by arrows 280 and 289) as described above. Rotation of bone anchor 250 within slot 222 is unrestricted, allowing bone anchor 250 to rotate freely (360+ degrees) as shown by arrow 286 which corresponds to lateral spinal twisting. The bone anchor 250 rotates freely around the longitudinal axis of the bone anchor. The range of angular motion 286 is not limited in this embodiment. However, features to limit such rotation could be designed into one or more of bone anchor 250 and housing 220. The desired range of rotation 286, can be selected, (if necessary) based upon the anatomical and functional needs of a patient.
  • FIGS. 3A-3F show views of a two-level adaptive stabilization system including an adaptive spinal rod according to an embodiment of the present invention. FIGS. 3A-3C show views of the first segment and components. FIG. 3D shows the second segment. FIG. 3E shows a compatible bone. FIG. 3F shows a perspective view of a spinal prosthesis including both segments of the two-level adaptive spinal rod of FIGS. 3A-3E.
  • Referring first to FIG. 3A, which is an exploded view of the components of the first segment 300 a of an adaptive spinal rod 300. First segment 300 a includes rods 311 a, housing 320 a, ball 330 a and cap 340 a. Rods 311 a are connected to either side of housing 320 a. Rods 311 a are similar in shape and material to standard spinal rods. Rods 311 a are adapted for mounting to the second segment 300 b (See FIG. 3D) of adaptive spinal rod 300 (See FIG. 3D). Rods 311 a are, in preferred embodiments, preferably cylinders about 4 mm to 4.5 mm in diameter and from 35 mm to 100 mm in length. Housing 320 a is preferably in the form of a flattened disc. Housing 320 a has a slot 322 a passing there through (similar in design in function to slot 122 of FIG. 1A). Slot 322 a is shaped to receive ball 330 a. Cap 340 a is adapted to fit within slot 322 a of housing 320 a. Cap 340 a has a cap slot 342 a therethrough (see, e.g. cap 140 of FIG. 1A).
  • FIG. 3B shows an enlarged view of ball 330 a. Ball 330 a is in the form of a sphere truncated on two opposing sides 332 a, 334 a. An aperture 336 a passes through ball 330 a from side 332 a to side 334 a. As shown in FIG. 3B, ball 330 a includes a rim 333 a surrounding aperture 336 a on side 332 a and a rim 335 a surrounding aperture 336 a on side 334 a. Ball 330 a is adapted to be secured to a shaft (mount 356 of FIG. 3E) with a separate nut. In alternative embodiments, aperture 336 a is provided with tool engagement features and/or threads and is adapted to be secured to a threaded shaft (not shown) without a separate threaded nut/fastener (not shown). Rim 333 a and rim 335 a are configured to interaction with the housing 320 a and cap 340 a to control range of motion. The dimensions of rim 333 a and rim 335 a are thus selected based on the range of motion desired. In general, where the rim has a larger outside the diameter it will there is less clearance between the rim and the housing 320 a and/or cap 340 a and therefore less range of motion.
  • As shown in FIG. 3C, during assembly, ball 330 a is placed into slot 322 a of housing 320 a. Cap 340 a is then secured into slot 322 a of housing 320 a trapping/containing ball 330 a between cap 340 a and housing 320 a. FIG. 3C shows first segment 300 a fully assembled—ball 330 a is positioned between cap 340 a and housing 320 a. Slot 322 a of housing 320 a and slot 342 a of cap 340 a cooperate to form a linear race 302 a in which ball 330 a is trapped/contained. Although ball 330 a is trapped within race 302 a, ball 330 a can pivot, slide, and rotate within race 302 a. In combination, the surface of ball 330 a, and the race 302 a form a sliding ball-joint 301 a. It is to be understood that the slot 322 a and thus, race 302 a can be linear and also can be configured in accordance with the various configurations of slot 122 and linear race 102 shown and described in the embodiments of FIGS. 1A-1H. Aperture 336 a of ball 330 a is accessible and configured for mounting adaptive spinal rod 300 to a pedicle screw (See, FIG. 3F).
  • FIG. 3D shows a perspective view of the second segment 300 b of an adaptive spinal rod 300. Second segment 300 b includes rod 310 b, housing 320 b, ball 330 b and cap 340 b. Rod 310 b is connected to the middle of housing 320 b. Rod 310 b is preferably similar in shape and material to a standard spinal rod. Rod 310 b is adapted for mounting to a standard spinal screw/pedicle screw. Rod 310 b is, in preferred embodiments, a cylinder about 5 mm to 6.5 mm in diameter and from 35 mm to 150 mm in length. Housing 320 b is preferably in the form of a flattened disc. Housing 320 b and cap 340 b trap or contain ball 330 b. Housing 320 b and cap 340 b cooperate to form a linear race 302 b in which ball 330 can slide, pivot and rotate. Ball 330 b and linear race 302 b together comprise a ball-joint 301 b. Ball 330 b is of the same design as ball 330 a (See FIG. 3B). Ball 330 b includes an aperture 336 b for securing a bone anchor.
  • On either side of housing 320 b are bores 322 b. Bores 322 b run parallel to rod 310 b and pass through housing 320 b. Bores 322 b are configured to receive rods 311 a of first segment 300 a (see FIG. 3A) in a sliding fashion. Each of bores 322 b intersects with a threaded bore 324 b. A set screw 326 b is provided for each of threaded bores 324 b. The set screws 326 b when driven in threaded bores 324 b are adapted to intersect bores 322 b and engage and lock rods 311 a of first segment 300 a (see FIG. 3A).
  • FIG. 3E, shows a bone anchor 350 configured for attachment of adaptive spinal rod 300 to a vertebra. As shown in FIG. 3E, bone anchor 350 includes a threaded shaft 352 at the distal end. Threaded shaft 352 is sized and configured for engaging a vertebra. In preferred embodiments threaded shaft 352 is sized and configured for implantation in the pedicle of a vertebra. Attached to threaded shaft 352 is head 354. Head 354 includes surface features 355 which permit head to be engaged by a tool to rotate head 354 and threaded shaft 352 and drive bone anchor 350 into a desired implant location. Protruding proximally from head 354 is a mount 356. Mount 356 has a smooth exterior surface to receive ball 330 of FIG. 3B. Protruding proximally of mount 356 is a threaded shaft 357 for attaching a nut 359. In the proximal end of threaded shaft 357 is an aperture 358. Aperture 358 is shaped such that the aperture 358 can be engaged by a driver for implanting/removing bone anchor 350 and/or attaching nut 359. For example, aperture 358 has, in some embodiments, a hexagonal or octagonal cross-section.
  • FIG. 3G is a partial sectional view of adaptive spinal rod 300 through ball 330 a and housing 320 a illustration features which serve to limit angulation of a bone anchor 350 relative to housing 320 a. FIG. 3G shows bone anchor 350 at one limit to its range of angulation with respect to housing 320 a. At the limit of angulation, rim 335 a contacts limit surface 328 a of housing 320 a. Additionally, in some embodiments, rim 333 a of ball 330 a comes into contact with a limit surface 348 a of cap 340 a. In preferred embodiments, to reduce wear, limit surfaces 328 a and 348 a are substantially parallel to the surface of rims 333 a and 335 a of ball 330 a with which they make contact when the rims and limit surfaces make contact. Note also that nut 359 is designed so as not to make contact with housing 320 a or cap 340 a even at the limit of angulation. In the embodiment shown in FIG. 3G, nut 359 has a relief 351 to prevent contact between nut 359 and cap 340 a. Note further that screw 350 is also designed so as not to make contact with housing 320 a or cap 340 a even at the limit of angulation. In the embodiment shown in FIG. 3G, head 354 has a relief 353 to prevent contact between head 354 and housing 320 a. In alternative embodiments, limit surfaces are provided on the bone screw and/or nut and/or another device, for example a washer. The limit surfaces are position to contact e.g. the housing or cap of an adaptive spinal rod to limit the range of motion in one or more axes.
  • FIG. 3F shows a spinal prosthesis 304 incorporating adaptive spinal rod 300. As shown in FIG. 3F, the first segment 300 a of the adaptive spinal rod 300 is mounted by a bone anchor 350 a to vertebra 192 a. The second segment 300 b of the adaptive spinal rod 300 is mounted by a bone anchor 350 b to vertebra 192 b. Rods 311 a of first segment 300 a pass through the housing 320 b of second segment 300 b. When distance between first housing 320 a and second housing 320 b is suitable for the functional and anatomic needs of the patient, set screws 326 b are tightened thereby locking rods 311 a in place. Rod 310 b of second segment 300 b is secured to vertebra 192 c by a convention spinal screw 370 as previously described.
  • After implantation and assembly, rod 310 b housing 320 b, rods 311 a and housing 320 a are all held in substantially fixed relationship to vertebra 192 c by spinal screw 370. However sliding ball-joint 301 b enables the bone anchor 350 b implanted in vertebra 192 b to slide, pivot and rotate relative to housing 320 b. Also, sliding ball-joint 301 a enables the bone anchor 350 a implanted in vertebra 192 a to slide, pivot and rotate relative to housing 320 a. The kinematics of both sliding ball-joints 301 a and 301 b are substantially as described in FIGS. 1E-1G and accompanying text. This embodiment of a spinal prosthesis 304 is suitable for use for example, where vertebrae 192 a, 192 b and 192 c are not to be fused together. The spinal prosthesis is adapted to provide load-sharing while allowing motion thereby stabilizing a level of the spine 190 while restoring and/or preserving some natural motion of the vertebrae 192 a, 192 b, 192 c. This configuration can, in some embodiments, be utilized to prevent adjacent segment deterioration by supporting a spinal motion segment adjacent a spinal fusion.
  • FIG. 3H shows an alternative single level adaptive spinal rod 300 h. Adaptive spinal rod has almost all components in common with adaptive spinal rod 300 of FIGS. 3A-3F. Adaptive spinal rod 300 h includes all of first segment 300 a of FIGS. 3A-3C. Adaptive spinal rod 300 h includes most of second segment 300 b of FIG. 3D. However, in second segment 300 b, rod 310 b and housing 320 b are replaced with a housing 320 h which does not include a rod for attachment to a conventional spinal screw on an adjacent level. Adaptive spinal rod 300 h is suitable for mounting to bone anchors 350 a, 350 b (of the same design as bone anchor 350 of FIG. 3E) implanted in adjacent vertebrae. The spacing between housing 320 h and housing 320 a is adjustable as previously described. After locking the spacing of housing 320 h and housing 320 a, the sliding ball joints 301 a, 301 h enable each of the bone anchors 350 to slide, pivot and rotate relative to housings 320 a, 320 b and rods 311 a. The kinematics of both sliding ball-joints 301 a and 301 h are substantially as described in FIGS. 1E-1G and accompanying text.
  • FIGS. 4A-4C show views of an alternative two-level adaptive stabilization rod according to an embodiment of the present invention. FIG. 4A shows an exploded view of first segment and components. FIG. 4B shows an exploded view of the second segment. FIG. 4C shows a perspective view of an assembly including both segments of the two-level adaptive spinal rod of FIGS. 4A-4B.
  • Referring first to FIG. 4A, which is an exploded view of the components of the first segment 400 a of an adaptive spinal rod 400. First segment 400 a includes rod 410 a, housing 420 a, ball 430 a and cap 440 a. Rod 410 a is connected to one side of housing 420 a. Rod 410 a is similar in shape and material to standard spinal rods. Rod 410 a is adapted for mounting to the second segment 400 b (See FIG. 4B) of adaptive spinal rod 400 (See FIG. 4C). Rod 410 a is, in a preferred embodiment, a cylinder about 5 mm to 6.5 mm in diameter and from 45 mm to 100 mm in length. Housing 420 a is preferably in the form of a flattened disc having a lateral extension from which rod 410 a protrudes. Housing 420 a has a slot 422 a passing there through (similar in design in function to slot 122 of FIG. 1A). Slot 422 a is shaped to receive ball 430 a. The long axis of slot 422 is parallel to the long axis of rod 410 a. Cap 440 a is adapted to fit within slot 422 a of housing 420 a. Cap 440 a has a cap slot 442 a there through (see, e.g. cap 140 of FIG. 1A). Ball 430 a is of the same configuration as previously described with respect to FIG. 3B.
  • During assembly, ball 430 a is placed into slot 422 a of housing 420 a. Cap 440 a is then secured into slot 422 a of housing 420 a trapping or containing ball 430 a between cap 440 a and housing 420 a. Slot 422 a of housing 420 a and slot 442 a of cap 440 a cooperate to from a linear race 402 a in which ball 430 a is trapped or contained. Although ball 430 a is trapped within race 402 a, ball 430 a can pivot and rotate within race 402 a. In combination, the surface of ball 430 a, and the linear race 402 a form a sliding ball-joint 401 a. It is to be understood that slot 422 a and thus race 402 a can be linear and also can be configured in accordance with the various configurations of slot 122 and linear race 102 shown in the embodiments of FIGS. 1A-1H. Aperture 436 a of ball 430 a is accessible and configured for mounting adaptive spinal rod 400 to a threaded shaft of a pedicle screw such as shown in FIG. 3E.
  • FIG. 4B shows an exploded view of the second segment 400 b of an adaptive spinal rod 400. Second segment 400 b includes rod 410 b, housing 420 b, ball 430 b and cap 440 b. Rod 410 b is connected to the middle of housing 420 b. Rod 410 b is similar in shape and material to a standard spinal rod. Rod 410 b is adapted for mounting to a standard spinal screw/pedicle screw. Rod 410 b is, in preferred embodiments, a cylinder about 5 mm to 6.5 mm in diameter and from 45 mm to 150 mm in length. Housing 420 b is preferably in the form of a flattened disc. On one side of housing 420 b is a bore 423 b. Bore 423 b runs parallel to rod 410 b and passes through housing 420 b. Bore 423 b is configured to receive rod 410 a of first segment 400 a (see FIG. 4A) in a sliding fashion. Bore 423 b intersects with a threaded bore 424 b. A set screw 426 b is provided for threaded bore 424 b. The set screw 426 b when driven in threaded bores 424 b is adapted to intersect bore 423 b and engage and lock rod 410 a of first segment 400 a (see FIG. 4A).
  • FIG. 4C shows two-level adaptive spinal rod 400 fully assembled. Ball 430 a, slot 422 a and cap 440 a have been assembled to create sliding ball-joint 401 a. Ball 430 b, slot 422 b and cap 440 b have been assembled to create sliding ball-joint 401 b which is similar in design and function to sliding ball-joint 401 a. Rod 410 a of first segment 400 a passes through bore 423 b of housing 420 b of second segment 400 b. The distance between first housing 420 a and second housing 420 b can be adjusted as suitable for the functional and anatomic needs of the patient. Set screw 426 b is subsequently tightened thereby locking rod 410 b to housing 420 b and fixing the distance between housing 420 a and housing 420 b.
  • FIG. 4D shows an example of a two-level spinal prosthesis incorporating two-level adaptive spinal rod 400. Adaptive spinal rod 400 is used, in some embodiments, in combination with two bone anchors 350 a, 350 b as shown in FIG. 3E and a conventional pedicle screw 370 to create an adaptive spinal prosthesis 404 similar to the adaptive spinal prosthesis shown in FIG. 3F. The first segment 400 a of the adaptive spinal rod 400 is mounted by a bone anchor 350 to a first vertebra (not shown). The second segment 400 b of the adaptive spinal rod 400 is mounted by a bone anchor 350 b to an adjacent vertebra (not shown). The rod 410 b of second segment 400 b is secured to a third vertebra using a conventional pedicle screw 370. After implantation and assembly, rod 410 b housing 420 b, rod 410 a and housing 420 a are all held in substantially fixed relationship to the third vertebra. However sliding ball-joints 401 a and 401 b permit the bone anchors 350 a, 350 b to which they are connected to slide (arrows 380 a, 380 b), pivot (arrows 382 a, 382 b) and rotate (arrows 384 a, 384 b) independently of one another. The kinematics of both sliding ball-joints 401 a and 401 b are substantially as described in FIGS. 1E-1G and accompanying text. The spinal prosthesis is adapted to provide load-sharing while allowing motion thereby stabilizing a level of the spine 190 while restoring and/or preserving some natural motion of the vertebrae.
  • FIGS. 5A-5B show views of an alternative two-level adaptive spinal rod according to an embodiment of the present invention. FIG. 5A shows an exploded view of the two-level adaptive stabilization system. FIG. 5B shows a perspective view of the assembled two-level adaptive spinal rod of FIG. 5A according to an embodiment of the present invention.
  • Referring first to FIG. 5A, which is an exploded view of the components of an adaptive spinal rod 500. Adaptive spinal rod 500 includes rod 510, housing 520, ball 530 a, ball 530 b, and cap 540. Rod 510 is connected to the end of housing 520. Rod 510 is similar in shape and material to standard spinal rods. Rod 510 is adapted for mounting to a conventional spinal screw. Rod 510 is, in a preferred embodiment, a cylinder about 5 mm to 6.5 mm in diameter and from 55 mm to 100 mm in length. Housing 520 is preferably in the form of an elongated flattened disc. Housing 520 has a slot 522 passing there through similar in design in function, but substantially longer than slot 122 of FIG. 1A. In embodiments slot 522 is between 30 mm and 120 mm in length. Slot 522 is shaped to receive both balls 530 a and 530 b. The long axis of slot 522 is parallel to the long axis of rod 510. Cap 540 is adapted to fit within slot 522 of housing 520. Cap 540 has a cap slot 542 there through. Balls 530 a and 530 b are of the same configuration as previously described with respect to FIG. 3B.
  • During assembly, balls 530 a and 530 b are placed into slot 522 of housing 520. Cap 540 is then secured into slot 522 of housing 520 trapping or containing balls 530 a and 530 b between cap 540 and housing 520. Slot 522 of housing 520 and slot 542 of cap 540 cooperate to form an elongated race 502 in which balls 530 a and 530 b are both trapped or contained. Although balls 530 a and 530 b are trapped within race 502, balls 530 a and 530 b can pivot and rotate within race 502. In combination, the surface of balls 530 a and 530 b, and the linear race 502 form an extended sliding ball-joint 501. It is to be understood that slot 522 and thus race 502 can be linear and also can be configured in accordance with the various configurations of slot 122 and linear race 102 shown in the embodiments of FIGS. 1A-1H. Bone anchors 350 a, 350 b are secured to balls 530 a and 530 b are accessible and configured for mounting adaptive spinal rod 500 to the threaded shafts of two pedicle screws such as shown in FIG. 3E. FIG. 5B shows two-level adaptive spinal rod 500 fully assembled. Balls 530 a, 530 b, slot 522 and cap 540 have been assembled to create sliding ball-joint 501. The distance between balls 530 a and 530 b can be adjusted as suitable for the functional and anatomic needs of the patient.
  • FIGS. 5C, 5D and 5E show how bone anchors 350 a, 350 b are able to move with respect to rod 510 of two-level adaptive spinal rod 500 when assembled as a two-level adaptive spinal prosthesis 504. FIG. 5C shows a section through bone anchor 350 and adaptive spinal rod 500 in a substantially saggital plane. FIG. 5D shows a section through bone anchor 350 and adaptive spinal rod 500 in a transverse plane. FIG. 5E shows a section through bone anchor 350 and adaptive spinal rod 500 in a substantially dorsal plane through the middle of the housing 520.
  • As shown in FIG. 5C, two-level adaptive spinal rod 500 can be used in combination with two bone anchors 350 a, 350 b (as described with respect to FIG. 3E) and a conventional spinal screw 170 (as, for example described with respect to FIG. 1D) to create an adaptive spinal prosthesis 504 similar to the adaptive spinal prosthesis shown in FIG. 3F. The first ball 530 a of the adaptive spinal rod 500 is mounted by a bone anchor 350 a to a first vertebra (not shown). The second ball 530 b of the adaptive spinal rod 500 is mounted by another bone anchor 350 b to an adjacent vertebra (not shown). The rod 510 of the adaptive spinal rod 500 is secured to a third vertebra (not shown) using a conventional spinal screw 170. After implantation and assembly, rod 510 and housing 520 b are held in a substantially fixed relationship to the third vertebra. However the motion of balls 530 a and 530 b within sliding ball-joint 501 permits the bone anchors to which they are connected to slide, pivot and rotate.
  • Referring again to FIG. 5C which shows a section through an adaptive spinal prosthesis 504 in a substantially saggital plane (vertical and including the longitudinal axis of bone anchors 350 a, 350 b). As shown in FIG. 5C, balls 530 a, 530 b are trapped or contained in linear race 502 formed by cap 540 in conjunction with housing 520. Balls 530 a, 530 b can move within race 502. Bone anchors 350 a, 350 b are mounted to balls 530 a, 530 b and thus can move relative to rod 510 with one angular degree of freedom and one linear degree of freedom shown in this view.
  • In the saggital plane shown in FIG. 5C, the linear motion of balls 530 a, 530 b within race 502 allows bone anchors 350 a, 350 b a limited vertical range of movement (shown by arrows 580) equal to the linear travel of balls 530 a, 530 b within race 502. The range of vertical motion is limited by the length of linear race 502. The desired range of vertical motion 580, and thus the length of the race 502, is selected based upon the anatomical and functional needs of a patient. In this embodiment, however, linear race 502 is sufficiently long to span between vertebrae. Thus, although the maximum distance between balls 530 a, 530 b is constrained, balls 530 a and 530 b are relatively unconstrained in movement towards one another.
  • In the saggital plane shown in FIG. 5C, the pivoting of balls 530 a, 530 b within race 502 also allows each of bone anchors 350 a, 350 b a independent and limited angular range of movement which corresponds to spinal flexion/extension (shown by arrows 582). The center of balls 530 a, 530 b is the center of rotation. The range of angular motion 582 is limited by interference between one or more of balls 530 a, 530 b and bone anchor 350 with housing 520. The desired range of angular motion 582, and thus the shape of balls 530 a, 530 b, bone anchor 350 and housing 520, is selected based upon the anatomical and functional needs of a patient.
  • Referring next to FIG. 5D which shows a section through bone anchor 350 a and adaptive spinal rod 500 in a substantially transverse plane (horizontal and including the longitudinal axis of bone anchor 350 a). The kinematics of bone anchor 350 b are substantially similar to that of bone anchor 350 a. As shown in FIG. 5D, ball 530 a is trapped or contained in linear race 502 formed by cap 540 in conjunction with housing 520. Ball 530 a can move within race 502. Rod 510 is oriented either directly into or directly out of the page in this transverse view through housing 520. Bone anchor 350 a is mounted to balls 530 a and thus can move relative to housing 520 with one angular degree of freedom shown in this view.
  • In the transverse plane shown in FIG. 5D, the pivoting of ball 530 a within race 502 allows bone anchor 350 a a limited angular range of movement which corresponds to spinal rotation (shown by arrow 584). The center of ball 530 a is the center of rotation. The range of angular motion is limited by interference between one or more of ball 530 a and bone anchor 350 with housing 520. The desired range of angular motion 584, and thus the shape of ball 530 a, bone anchor 350 and housing 520, is selected based upon the anatomical and functional needs of a patient. In embodiments, the range of angular movement 584 in the transverse plane is limited to less than 20 degrees.
  • Referring next to FIG. 5E which shows a section through bone anchor 350 a and adaptive spinal rod 500 in a substantially dorsal plane (vertical and perpendicular to the longitudinal axis of bone anchors 350 a, 350 b). As shown in FIG. 5E, balls 530 a, 530 b are trapped or contained in linear race 502. Balls 530 a, 530 b can move within race 502. Bone anchors 350 a, 350 b are oriented either directly into or directly out of the page in this transverse view through housing 520. Bone anchors 350 a, 350 b are mounted to balls 530 a, 530 b and thus can move relative to rod 510 with one angular degree of freedom and one linear degree shown in this view.
  • In the dorsal plane shown in FIG. 5E, the linear motion of balls 530 a, 530 b within race 502 allows bone anchors 350 a, 350 b the limited vertical range of movement (shown by arrows 580) equal to the linear travel of balls 530 a, 530 b within race 502 as described above. Rotation of balls 530 a, 530 b within race 502 also allows bone anchors 350 a, 350 b to rotate freely an independently (360+ degrees) as shown by arrows 586 which corresponds to lateral spinal twisting. The bone anchors 350 a, 350 b and balls 530 a, 530 b rotate freely around the longitudinal axis of the bone anchors. The range of angular motion 586 is not limited in this embodiment. However features to limit such rotation could be designed into one or more of balls 530 a, 530 b and bone anchors 350 a, 350 b and housing 520. The desired range of angular motion 586, and thus the shape of balls 530 a, 530 b, bone anchors 350 a, 350 b and housing 520, can be selected, if necessary) based upon the anatomical and functional needs of a patient.
  • FIGS. 5F, 5G and 5H relate to a modification to the two-level adaptive spinal rod of FIGS. 5A-5E incorporating a spacer. FIG. 5F is a perspective view the spacer. FIG. 5G shows the spacer in combination with the two-level adaptive spinal rod of FIGS. 5A-5E. FIG. 5H shows a sectional view through the modified adaptive spinal rod.
  • Referring first to FIG. 5F which is a perspective view of a spacer 590. As shown in FIG. 5F, spacer 590 has two parallel sides 592, 593. Parallel side 592, 593 are convex. The curvature of sides 592, 593 is selected to engage the curvature of the linear race 502. Sides 592, 593 are spaced such that spacer 590 can fit within linear race 502 and slide along linear race 502. Spacer 590 is, in some embodiments, made from a biocompatible metal, for example, titanium, titanium alloy and/or cobalt chrome. The other two sides 594, 595 of spacer 590 are concave. The surface of sides 594, 595 is selected to engage the surfaces of balls 530 a, 530 b. The thickness of spacer 590 is substantially the thickness of linear race 502.
  • Referring to FIG. 5G which shows spacer 590 assembled with the two-level adaptive spinal rod 500 of FIGS. 5A-5E. As shown in FIG. 5G, spacer 590 fits within linear-race 502 between balls 530 a and 530 b. Convex sides 592, 593 of spacer 590 engage and slide within the sides of linear race 502. Spacer 590 can slide along linear race 502 as shown by arrow 596. The sides 594, 595 are positioned to contact balls 530 a, 530 b and limit the travel of balls 530 a, 530 b toward one another. Thus, spacer 590 serves to constrain somewhat the range of motion of balls 530 a, 530 b and limit extension of the spine.
  • FIG. 5H shows a section through bone anchors 350 a, 350 b and adaptive spinal rod 500 including spacer 590 in a substantially dorsal plane (vertical and perpendicular to the longitudinal axis of bone anchors 350 a, 350 b). As shown in FIG. 5H, balls 530 a, 530 b are trapped or contained in linear race 502. Spacer 590 is positioned between balls 530, 530 b Balls 530 a, 530 b can move within race 502. In the dorsal plane shown in FIG. 5E, the linear motion of balls 530 a, 530 b within race 502 allows bone anchors 350 a, 350 b the limited vertical range of movement shown by arrows 581 equal to the linear travel of balls 530 a, 530 b within race 502 but constrained by the presence of spacer 590. Note that the range of motion 581 is reduced compared to range of motion 580 of FIG. 5E because of the presence of spacer 590. The range of linear motion 181 is limited by interference between one or more of ball 350 a, ball 350 b, and spacer 590 with housing 520. The desired range of angular motion 581, and thus the shape of balls 530 a, 530 b, spacer 590 and housing 520, is selected based upon the anatomical and functional needs of a patient. In embodiments, the range of linear movement is limited to less than 10 mm. In preferred embodiments, the range of linear movement 581 is limited to less than 4 mm.
  • Rotation of balls 530 a, 530 b within race 502 still allows bone anchors 350 a, 350 b to rotate freely an independently (360+ degrees) as shown by arrows 586 which corresponds to lateral spinal twisting. The desired range of angular motion 586, and thus the shape of balls 530 a, 530 b, bone anchors 350 a, 350 b and housing 520, can be selected, if necessary) based upon the anatomical and functional needs of a patient.
  • In alternative embodiments, single-level adaptive spinal rods are connected using one or more connectors to assemble a multi-level adaptive spinal prosthesis. A range of polyaxial connectors adaptable for this purpose is disclosed in U.S. patent application Ser. No. 12/566,485 titled “Versatile Polyaxial Connector Assembly And Method For Dynamic Stabilization Of The Spine” to Mitchell et al. FIGS. 6A-6G show views of a polyaxial connector 660, suitable for use with bone anchor 650 and adaptive spinal rod 600 as part of a multi-level adaptive spinal prosthesis (see FIG. 6G). Connector 660 mounts externally to a second mount of a bone anchor 650. FIG. 6A shows an example of an adaptive spinal rod 600. FIG. 6B shows a two-mount bone anchor 650 suitable for use with adaptive spinal rod 600 and connector 66. FIG. 6C shows an exploded view of a connector 660, and components thereof. FIG. 6D shows a perspective view of connector 660 as assembled. FIGS. 6E and 6F illustrate operation of the connector 660. FIG. 6G shows a two-level adaptive spinal prosthesis using the components of FIGS. 6A-6F.
  • Referring first to FIG. 6A, which shows a single level adaptive spinal rod 600. Adaptive spinal rod 600 includes rod 610, housing 620, arm 621, ball 630 (see e.g. ball 330 of FIG. 3B) and cap 640. Rod 610 is connected to one side of housing 620. Rod 610 is similar in shape and material to standard spinal rods. Rod 610 is adapted for mounting to a connector or spinal screw (not shown). Rod 610 is, in a preferred embodiment, a cylinder about 5 mm to 6.5 mm in diameter and from 65 mm to 100 mm in length. An arm 621 projects laterally from housing 620 and connects to rod 610.
  • Housing 620 is preferably in the form of a flattened disc. Housing 620 has a slot 622 passing therethrough (similar in design in function to slot 122 of FIG. 1A). Slot 622 is shaped to receive ball 630. The long axis of slot 622 is parallel to the long axis of rod 610. Cap 640 is adapted to fit within slot 622 of housing 620. As shown in FIG. 6A, cap 640 and housing 620 cooperate to form race 602 in which ball 630 is trapped to form a linear ball-joint as previous described. Although ball 630 is trapped within race 602, ball 630 can pivot and rotate within race 602. It is to be understood that slot 622 and thus race 602 can be linear and also can be configured in accordance with the various configurations of slot 122 and linear race 102 shown in the various embodiments of FIGS. 1A-1H. Aperture 636 of ball 630 is accessible and configured for mounting adaptive spinal rod 600 to a bone anchor (see, e.g., FIG. 6B).
  • FIG. 6B, shows a bone anchor 650 configured for attachment of adaptive spinal rod 600 to a vertebra through a connector (not shown). As shown in FIG. 6B, bone anchor 650 includes a threaded shaft 652 at the distal end. Threaded shaft 652 is sized and configured for engaging a vertebra. In preferred embodiments threaded shaft 652 is sized and configured for implantation in the pedicle of a vertebra. Attached to threaded shaft 652 is head 654. Head 654 includes splines 655 which permit head to engage a connector in a fixed angular position. Protruding proximally from head 654 is a second mount 651. Second mount 651 is designed to be received in and engaged by connector 660 of FIGS. 6C and 6D. Second mount 651 is threaded in order that the connector can be secured to second mount
  • Protruding proximally from second mount 651 is first mount 656. First mount 656 has a smooth exterior surface to receive ball 630 of FIG. 6A. Protruding proximally of first mount 656 is a threaded shaft 657 for attaching a nut 659 to secure ball 630 of FIG. 6A. In the proximal end of threaded shaft 657 is an aperture 658. Aperture 658 is shaped such that the aperture 658 can be engaged by a driver for implanting/removing bone anchor 650 and/or attaching nut 659. For example, aperture 658 has, in some embodiments, a hexagonal or octagonal cross-section.
  • Referring next to FIGS. 6C and 6D, which show respectively an exploded and assembled view of connector 660. The components of connector 660 include: snap ring 662, set screw 677, clamp ring 661, swivel 670 and ring nut 680. As shown in FIG. 6C, clamp ring 661 is generally annular with a bore 669. Bore 669 of clamp ring 661 is sized such that the clamp ring 661 can slide over second mount 651 of bone anchor 650 and also receive the distal end 682 of ring nut 680. Clamp ring 661 can rotate around the second mount 651 before the clamp ring 661 is locked in place by ring nut 680. Clamp ring 661 has a plurality of splines 667 on a distal surface for engaging splines 655 of bone anchor 650. Clamp ring 661 has a cylindrical extension 664. Cylindrical extension 664 includes a saddle 665 and terminal groove 668. The groove 668 is sized to engage snap ring 662.
  • Swivel 670 has a channel 674 which passes through swivel 670 and which is sized to receive therethrough the rod of an adaptive spinal rod (or conventional spinal rod). Swivel 670 has a threaded aperture 678 sized to fit set screw 677. Threaded aperture 678 intersects channel 674 to allow set screw 677 to contact a spinal rod (not shown) within channel 674. A bore 671 passes through swivel 670 and intersects with channel 674. Bore 671 is sized to receive cylindrical extension 664 of clamp ring 661. Bore 671 has a lip 672 sized to engage snap ring 662. Snap ring 662 is designed to fit engage groove 668 of cylindrical extension 664 and lip 672 of bore 671 to secure cylindrical extension 664 within bore 671. Cylindrical extension 664 can, however, rotate within bore 671.
  • As shown in FIG. 6D, ring nut 680 is received within bore 669 of clamp ring 661. Ring nut 680 is, in some embodiments, provided with a lip, groove, or other detent (not shown) to hold ring nut 680 within bore 669 while still allowing rotation of ring nut 680 relative to clamp ring 661. Ring nut 680 also has tool engagement features 684 which can be engaged by a tool/wrench to secure ring nut 680 to second mount 651 of bone anchor 650 (see FIG. 6B). Cylindrical extension 664 is received through bore 671 and held in place by snap ring 662. Set screw 672 is received within threaded aperture 678 of swivel 670.
  • FIGS. 6E and 6F illustrate the mounting of connector 660 to rod 610 and to the second mount 651 of bone anchor 650. As shown in FIG. 6E, rod 610 (shown in section) is received in channel 674 of connector 660. Second mount 651 is received in clamp ring 661. During implantation, clamp ring 661 can rotate around bone anchor 650. The unclamped configuration allows adjustment of the direction of rod 610 and also allows rod 610 to slide through channel 674, and also allows swivel 670 to rotate around cylindrical extension 664. When ring nut 680 is tightened, splines 655 are forced against splines 667 locking clamp ring 661 to second mount 651 and preventing further rotation around bone anchor 650. When set screw 677 is tightened, it forces rod 610 against saddle 665, locking rod 610 in position. Set screw 677 also forces splines of cylindrical extension 664 against splines 675 of swivel 670 locking swivel 670 in position relative to clamp ring 661. Operation of the ring nut 680 and set screw 677 serves to place the connector 660 in a clamped configuration and lock the clamp ring 661 to the second mount 651 of the bone anchor 650, lock swivel 670 in a fixed position relative to clamp ring 661 and secure rod 610 within the channel 674 of connector 660.
  • The connector 660 of FIGS. 6C-6F may be used, in some embodiments, to construct an adaptive stabilization assembly for one or more levels of the spine of a patient. FIG. 6G shows an example of a two-level adaptive stabilization assembly 690 utilizing the connector 660 of FIGS. 6C-6F. FIG. 6G shows how the components may be assembled to provide a multilevel adaptive stabilization assembly which provides stabilization of the spine and load sharing while preserving motion. Note that an identical or similar construct would preferably be implanted on each side of the spine.
  • As shown in FIG. 6G, rod 110 of adaptive spinal rod 100 is mounted to head 174 of spinal screw 170. Ball 130 of adaptive spinal rod 100 is secured to bone anchor 650 by nut 659. Sliding ball-joint 101 permits bone anchor 650 to slide, pivot and rotate relative to spinal screw 170. Connector 660 is also mounted to bone anchor 650. Ring nut 680 (not shown) secures clamp ring 661 of connector 660 to bone anchor 650. Set screw 677 secures rod 610 of adaptive spinal rod 600 within channel 674 of swivel 670. Ball 630 of adaptive spinal rod 600 is secured to bone anchor 350 by nut 359. Sliding ball-joint 601 permits bone anchor 650 to slide pivot and rotate relative to bone anchor 350.
  • As also shown in FIG. 6G, ball 630 of adaptive spinal rod 600 is secured to bone anchor 350 by nut 359. Rod 110 is positioned within channel 674 of connector 660. The position of the rod 610 is then adjusted relative to connector 660 prior to tightening set screw 677. Adaptive stabilization assembly 690 spans two vertebrae two levels of the spine (three vertebrae). Connector 660 and adaptive spinal rods 100, 600 permit assembly of adaptive stabilization assembly 690 for a wide range of different patient anatomies and/or placement of bone anchors 350, 650 and spinal screw 170. Connector 660 is particularly useful where, as here, there is slight lateral displacement between the bone anchor positions on either side of a level.
  • Adaptive spinal prosthesis 690 is typically assembled in vivo by first implanting the bone anchors 650, 350 and spinal screw 170 in pedicles of adjacent vertebra. After implanting the bone anchors 650, 350 and spinal screw 170, the connector 660 is placed over bone anchor 650 and rod 610 is positioned within channel 674 of the connector 660. Ball 630 is then secured to bone anchor 350. After securing ball 630, the position of rod 610 and swivel 670 are adjusted and then connector 660 is locked in position by tightening set screw 677 and tightening ring nut 680 (not shown). Rod 110 is then secured to head 174 of spinal screw 170 by tightening set screw 173.
  • FIGS. 7A-7C are views of an adaptive stabilization system including an adaptive spinal rod according to an alternative embodiment of the present invention. FIG. 7A is an exploded view showing the components of an adaptive spinal rod. FIG. 7B is a perspective view of the assembled adaptive spinal rod. FIG. 7C is a sectional view illustrating the kinematics of a bone anchor relative to the adaptive spinal rod.
  • Referring first to FIG. 7A, which is an exploded view of the components of an adaptive spinal rod 700. Adaptive spinal rod 700 includes: rod 710, housing 720, ball 730, cap 740, spacer 750 and set screw 760. Rod 710 is connected at one end to housing 720. Rod 710 is similar in size, shape and material to standard spinal rods. Rod 710 is adapted for mounting to a standard pedicle screw or polyaxial screw (not shown). Rod 710 is in preferred embodiments, preferably a cylinder about 5 mm to 6.5 mm in diameter and from 35 mm to 100 mm in length. In preferred embodiments, rod 710 and housing 720 are made in one piece from titanium or titanium alloy.
  • Housing 720 has a slot 722 passing there through. Slot 722 is shaped to receive ball 730 and spacer 750 from open side 724 however, the closed side 726 of slot 722 is too small for ball 730 and spacer 750 to pass. Open side 724 of slot 722 is also shaped to receive cap 740. Closed side 726 of slot 722 has a curved surface 728 adapted to engage ball 730. In one embodiment curved surface 728 has the same radius of curvature as ball 730. Housing 720 has a threaded aperture 721 for receiving set screw 760.
  • Ball 730 is in some embodiments, of the same design as ball 130 of FIG. 1A or ball 330 a of FIG. 3B. An aperture 736 passes through ball 730. In some embodiments the aperture is threaded in part and/or provided with tool engagement features (a hexagonal depression is shown) which allow ball 730 to be engaged and turned by a tool. Ball 730 is adapted to be secured to a bone anchor with or without using a separate nut depending on design.
  • Spacer 750 has two parallel sides 752, 753. Parallel side 752, 753 are convex. The curvature of sides 752, 753 is selected to engage the curvature of the linear race 502. Sides 752, 753 are spaced such that spacer 750 can fit within race 702 and slide along linear race 702. As discussed above, race 702 can have other configurations. Spacer 750 is, in some embodiments, made from a biocompatible metal, for example, titanium, titanium alloy and/or cobalt chrome. Side 754 of spacer 750 is concave for engaging ball 730. The remaining has an aperture 755 for engaging set screw 760. The thickness of spacer 750 is substantially the thickness of linear race 702. In alternative embodiments, set screw 760 is adapted to contact ball and directly limit the length of linear race 702 without the need for a spacer 750.
  • Cap 740 is adapted to fit within slot 722 of housing 720. Cap 740 has a cap slot 742 therethrough. The open side 744 of slot 742 is configured to admit a portion of ball 730 and spacer 750. The closed side 746 of slot 742 is too small for ball 730 and spacer 750 to pass. The interior of slot 742 has a curved surface adapted to engage ball 730 and spacer 750. During assembly, ball 730 and spacer 750 are placed into slot 722 of housing 720. Cap 740 is then secured into slot 722 of housing 720 trapping ball 730 and spacer 750 between cap 740 and housing 720.
  • FIG. 7B shows a fully assembled adaptive spinal rod 700 in which ball 730 and spacer 750 are positioned between cap 740 and housing 720. The position of spacer 750 is adjustably controlled by set screw 760. Slot 722 of housing 720 and slot 742 of cap 740 cooperate to from a linear race 702 in which ball 730 is contained or trapped. The position of spacer 750 controls the length of linear race 702. Although ball 730 is contained or trapped within linear race 702, ball 730 can pivot and rotate within race 702 as shown by arrows 760, 762. Ball 730 can also slide a small distance along linear race 702 as shown by arrow 764. The range of angular and linear movement of ball 730 can be adjusted by changing the length of linear race 702 using set screw 760 and spacer 750. In adaptive spinal rod 700 as assembled, aperture 736 of ball 730 is accessible and configured for mounting adaptive spinal rod 700 to a bone anchor, e.g. bone anchor 350 of FIG. 3E.
  • Referring next to FIG. 7C which shows a section through a bone anchor 350 and adaptive spinal rod 700 in a substantially dorsal plane (vertical and perpendicular to the longitudinal axis of bone anchor 350). As shown in FIG. 7C, ball 730 is contained or trapped in linear race 102. Set screw 760 is adjustable to move spacer 750 and control the length of race 702. Ball 730 can move within race 702. Bone anchor 350 is oriented either directly into or directly out of the page in this transverse view through housing 720. Bone anchor 350 is mounted to ball 730 and thus can move relative to rod 710 with one angular degree of freedom and one linear degree shown in this view.
  • In the dorsal plane shown in FIG. 7C, race 702 allows bone anchor 150 a limited vertical range of movement 780 corresponding to spinal flexion/extension. The range of linear motion can be adjusted using set screw 760 to more spacer 750. Rotation of ball 130 within race 702 is unrestricted, allowing bone anchor 350 to rotate freely (360+ degrees) as shown by arrow 786 which corresponds to lateral spinal twisting. The bone anchor 350 rotates freely around the longitudinal axis of the bone anchor 350. The range of rotation 786 is not limited in this embodiment. However features to limit such rotation could be designed into one or more of bone anchor 750, ball 730, cap 740, and housing 720. The desired range of linear motion 780 and rotation 786, can be selected, if necessary or desirable, based upon the anatomical and functional needs of a patient.
  • Implantation and Assembly Tools
  • The implantation and assembly of adaptive spinal rods is preferably performed in a minimally invasive manner and, thus, tools are provided to facilitate installation and assembly through cannulae. These tools can also be used in open procedures. One suitable minimally invasive approach to the lumbar spine is the paraspinal intermuscular approach. This approach is described for example in “The Paraspinal Sacraspinalis-Splitting Approach to the Lumber Spine,” by Leon L. Wiltse et al., The Journal of Bone & Joint Surgery, Vol. 50-A, No. 5, July 1968, which is incorporated herein by reference. In general the patient is positioned prone. Incisions are made posterior to the vertebrae to be stabilized. The dorsal fascia is opened and the paraspinal muscle is split to expose the facet joints and lateral processes of the vertebra. Bone anchors according to embodiments of the present invention and conventional pedicle screws are placed in the vertebrae as necessary for the selected assembly. The screws are placed lateral to the facet joints and angled in towards the vertebral body.
  • After placement of the screws, the adaptive spinal rods according to embodiments of the present invention are then inserted into position adjacent the bone anchors, screws and conventional pedicle screws. The balls of the adaptive spinal rods are then secured to the mounts of the bone anchors the other end of the adaptive spinal rod is then connected to the conventional screws with the desired interpediclular distance. The implantation of the adaptive bone anchors and connection of the adaptive rods can be facilitated by specially designed implantation tools (FIGS. 8A-8D) and connection tools (FIGS. 9A-9F) as described below.
  • FIG. 8A shows a perspective view of an implantation tool 850 for use in implanting a bone anchor 150. Bone anchor 150 is as described with respect to FIG. 1C with the addition of a tool engagement feature (not shown). Implantation tool 850 includes an inner shaft 860 received within a tubular sleeve 870. Inner shaft 860 is free to rotate within sleeve 870. Sleeve 870 may also be slid towards the proximal end of inner shaft 860 by pulling on grip 874. A coil spring 872 is connected between the sleeve 870 and inner shaft 860 to hold sleeve 870 in its more distal position relative to shaft 860. The length and diameter of implantation tool 850 is selected so as to allow use through a cannula in a minimally invasive surgical technique thereby reducing disruption of tissues adjacent the implantation site, reducing patient recovery and improving surgical outcomes.
  • Referring again to FIG. 8A, shaft 860 has at a proximal end a quick release mount 862 to which a handle (not shown) may be attached for turning inner shaft 860. Suitable handles for attachment to shaft 860 include ratcheting handles, torque sensing handles and torque limiting handles. In alternative embodiments, a handle may be permanently connected to or integrated with the proximal end of shaft 862. Inner shaft has at a distal end a head 864. Head 864 includes means for engaging and securing bone anchor 150 during implantation as is described below.
  • As also shown in FIG. 8A, head 864 can be received over the proximal portion of bone anchor 150 with key 158 and mount 156 received within shaft 860 (see dashed line). In use, bone anchor 150 is inserted into the head 864 of shaft 860 with the head 154 and engagement features 155 engaged by head 864 and the key 158 secured within head 864. Bone anchor 150 is thus secured to implantation tool 850. Bone anchor 150 will not be released unless and until the surgeon pulls back on grip 874. Thus, bone anchor 150 and implantation tool can be inserted as one unit through a cannula to the implantation location in the spine facilitating the positioning and implantation of bone anchor 150.
  • FIG. 8B shows a detailed sectional view of the head 864 of the implantation tool 850 of FIG. 8A engaged with a bone anchor 150. As shown in FIG. 8B, head 864 includes a socket 865 for receiving and engaging head 154 of bone anchor 150. Socket 865 is designed to mate with head 154 in order to rotate the threaded shaft 152 of bone anchor 150. Thus, the interior of socket 865 may be hexagonal, octagonal or provided with flutes/splines etc., depending on the particular configuration of the head 154. Socket 865 should be able to apply sufficient torque to head 154 to implant the bone anchor 150 in a pedicle.
  • Referring again to FIG. 8B, head 864 also includes a bore 865 for receiving key 158 and mount 156 of adaptive bone anchor. As shown in FIG. 8B, key 158 includes a nipple 818 at the proximal end. A ball 852 is positioned within an aperture 867 which passes from the exterior of shaft 860 intersecting bore 865 adjacent nipple 818. Ball 852 is held by sleeve 870 in a position in which ball 852 protrudes into bore 865 so as to trap nipple 818 within bore 865. In a preferred embodiment, there are three such balls, however, only one is shown in this sectional view. Thus, head 154 is received in socket 865 and bone anchor 150 is locked to implantation tool 850 by the interaction of nipple 818 and ball(s) 852.
  • FIG. 8C shows a detailed sectional view of the head 864 of the implantation tool 850 of FIG. 8A configured to release a bone anchor 150. After implantation of bone anchor 150 it is necessary to remove implantation tool 850. The first step is to slide sleeve 870 proximally relative to shaft 860 as shown by arrow A. This is achieved by pulling back on grip 874 against the force of spring 872 (See FIG. 8A). As sleeve 870 is pulled proximally, ball(s) 852 enters a portion of sleeve 870 with a larger internal diameter. Ball(s) 852 can move away from engagement with nipple 818 and key 158 as they pass ramp 865 releasing nipple 818. At this stage both shaft 860 and sleeve 870 can be pulled together away from bone anchor 150.
  • FIG. 8D shows a transverse view of the lumbar spine illustrating use of the implantation tool 850 of FIG. 8A to implant bone anchors 150 in the pedicles 882 of a lumbar vertebra 884 according to an embodiment of the invention. As shown in FIG. 8D, implantation tool 850 may be used through a cannula 880 to implant the adaptive bone anchor in a minimally invasive procedure. The cannula 880 is introduced to the patient to approach the pedicles posteriorly. The pedicle 882 of the vertebra is 884 is exposed in the conventional fashion. A hole 886 is then drilled through the pedicle 882 into the vertebral body 883 of the vertebra. Next, a bone anchor 150 is selected having of suitable length, diameter and force/deflection characteristics is selected for implantation. The head 154 of the selected bone anchor 150 is inserted into the head 864 of implantation tool 850 and secured in place.
  • Referring now to the left side of FIG. 8D, bone anchor 150 and implantation tool 850 are inserted as one assembly through cannula 880 to the implantation site. Then bone anchor 150 is implanted by turning a handle 888 attached to the quick release on the proximal end of shaft 860. The bone anchor 150 is driven into hole 886 until the head 154 is at the surface of the vertebra 884 (see arrow 890). The torque to drive bone anchor 150 is provided by handle 888 through shaft 860 to head 154 of bone anchor 150.
  • Referring now to the right side of FIG. 8D, when bone anchor 150 is correctly positioned in pedicle 882, the physician pulls back on grip 874 against the force of spring 872. Sleeve 870 moves proximally relative to shaft 860. Shaft 860 releases the grip on bone anchor 150 and then both shaft 860 and sleeve 870 move away from cannula 880 and out of the patient (see arrow 892). Bone anchor 150 is now correctly implanted and prepared for attachment to an adaptive spinal rod and/or other spinal stabilization assembly components.
  • FIGS. 9A-9D show views of an attachment tool for securing an adaptive spinal rod 100 to a bone anchor 150 according to an embodiment of the invention. FIG. 9A shows a perspective view of an attachment tool 950 for securing an adaptive spinal rod 100 to a bone anchor 150 (shown in FIG. 9C) according to an embodiment of the invention. Adaptive spinal rod 100 may be, for example, the adaptive spinal rod 100 of FIGS. 1A-1B. Bone anchor 150 may be, for example, the bone anchor 150 as shown in FIG. 1C.
  • Referring first to FIG. 9A, attachment tool 950 includes an inner shaft 960 received within a tubular sleeve 970. The length and diameter of attachment tool 950 is selected so as to allow use through a cannula in a minimally invasive surgical technique thereby reducing disruption of tissues adjacent the implantation site, reducing patient recovery time and improving surgical outcomes. Inner shaft 960 is free to rotate and slide within sleeve 970. Inner shaft 960 has at a proximal end an attached handle 962. In alternative embodiments shaft 960 may have a fitting to which a handle might be attached, for example, ratcheting handles, torque sensing handles and torque limiting handles Inner shaft has at a distal end a head 964 for engaging and securing the key of an adaptive spinal rod 100 (see FIG. 9B).
  • Referring again to FIG. 9A, sleeve 970 includes a butterfly grip 974 at the proximal end thereof. Sleeve 970, has at the distal end thereof, means for engaging and securing the female tool engagement features of a ball of an adaptive spinal rod 100 during connection to a bone anchor as is described below. In a preferred embodiment, head 964 includes a male hex fitting 972 with a central aperture 973. FIG. 9B shows an enlarged view of head 964 from the distal end of attachment tool 950. FIG. 9B shows male hex fitting 972 with central aperture 973. Through central aperture 973 is visible female hex socket 965 of head 964. Protruding into female hex socket 965 are two spring tabs 967.
  • FIGS. 9C and 9D show detailed sectional views of the distal end attachment tool 950 in relation to an adaptive spinal rod 100 and bone anchor 150. Referring first to FIG. 9C, which shows a detailed sectional view of the distal end of the attachment tool 950 of FIG. 9A, engaged with an adaptive spinal rod 100 and a bone anchor 150. As shown in FIG. 9C, male hex fitting 972 of head 964 of outer sleeve 970 fits into the tool engagement features of ball 130. At the same time the key 158 of bone anchor 150 is received within female hex socket 965 of inner shaft 960. When thus engaged, turning handle 962 relative to butterfly grip 974 (See FIG. 9A) can rotate ball 130 relative to bone anchor 150. Attachment tool 950 is designed to apply sufficient torque to ball 130 to secure ball 130 to bone anchor 150 and to breakaway key 158. In a preferred embodiment, attachment tool 950 should be able to provide greater than 30 foot pounds of torque.
  • FIG. 9D shows a detailed sectional view of the distal end of the attachment tool 950 of FIG. 9A after break away of key 158 of bone anchor 150. As shown in FIG. 9D, when ball 130 has been tightened onto bone anchor 150, tabs 967 on central aperture 973 engage either side of a nipple 818 of key 158 to secure key 158 within female hex socket 965. Thus, when key 158 breaks away it can be removed from the patient with connection tool 950 as shown.
  • FIGS. 9E-9F show lateral views of the lumbar spine illustrating steps of attaching an adaptive spinal rod 100 to a bone anchor 150 utilizing the attachment tool of FIG. 9A according to an embodiment of the invention. As shown in FIG. 9E, the adaptive spinal rod 100 is implanted after the bone anchor 150 and a polyaxial screw 940 have already been implanted. Adaptive spinal rod 100 is implanted in a cranial direction—preferably in a minimally invasive manner until adaptive spinal rod 100 is positioned adjacent bone anchor 150 and polyaxial screw 940. The key 158 of bone anchor 150 is then fed through ball 130 of adaptive spinal rod 100 as shown.
  • Next, as shown in FIG. 9F, connection tool 950 is inserted through a cannula 880 to engage ball 130 and key 158. Ball 130 is then turned relative to key 158 until it is fully secured to bone anchor 150. When ball 130 is fully secured to bone anchor 150, further torque is applied until key 158 (not shown) is sheared off. In a preferred embodiment, this requires 30 foot pounds of torque and is sufficient to lock ball 130 to bone anchor 150. Next, as shown in FIG. 9G, connection tool 950 can be removed from cannula 880. As previously described, key 158 (not shown) is retained inside attachment tool 950 for easy removal from the patient. As shown in FIG. 9H, a conventional tool 984 is then inserted through cannula 980 to operate polyaxial screw 940 to secure the other end of adaptive spinal rod 100.
  • Alternative Connector for Two-Level Spinal Prosthesis
  • In alternative embodiments, single-level adaptive spinal rods are connected using one or more connectors to assemble a multi-level adaptive spinal prosthesis. A range of polyaxial connectors adaptable for this purpose is disclosed in U.S. patent application Ser. No. 12/566,485 titled “Versatile Polyaxial Connector Assembly And Method For Dynamic Stabilization Of The Spine” to Mitchell et al. For example, FIGS. 10A-10G show views of a polyaxial connector 1060 adapted for connecting a bone anchor 1050 to an adaptive spinal rod 1000 in a two-level adaptive spinal prosthesis 1004. Connector 1060 mounts externally to a second mount of a bone anchor 1050. FIG. 10A shows an example of an adaptive spinal rod 1000. FIG. 10B shows a bone anchor 1050 suitable for use with adaptive spinal rod 1000 and a connector. FIGS. 10C and 10D shows an exploded view of a connector, and components thereof, suitable for use with bone anchor 1050 and adaptive spinal rod 1000 as part of a two-level adaptive spinal prosthesis. FIGS. 10E and 10F illustrate operation of the polyaxial connector. FIG. 10G shows a two-level adaptive spinal prosthesis 1090 using the components of FIGS. 10A-10F.
  • Referring first to FIG. 10A, which is an exploded view of the components of a single level adaptive spinal rod 1000. Adaptive spinal rod 1000 includes rod 1010, housing 1020, arm 1021, ball 330 (see FIG. 3B) and cap 1040 a. Rod 1010 a is connected to one side of housing 1020 a. Rod 1010 a is similar in shape and material to standard spinal rods. Rod 1010 a is adapted for mounting to the second segment 1000 b (See FIG. 10B) of adaptive spinal rod 1000 (See FIG. 10C). Rod 1010 is, in a preferred embodiment, a cylinder about 5 mm to 6.5 mm in diameter and from 105 mm to 100 mm in length. Housing 1020 is preferably in the form of a flattened disc. An arm projects laterally from housing 1020 and connects to rod 1010. Housing 1020 has a slot 1022 passing therethrough (similar in design in function to slot 122 of FIG. 1A). Slot 1022 is shaped to receive ball 1030. The long axis of slot 1022 is parallel to the long axis of rod 1010. Cap 1040 is adapted to fit within slot 1022 of housing 1020. As shown in FIG. 10A, cap 1040 and slot 1020 cooperate to form race 1002 in which ball 1030 is contained or trapped to form a linear ball-joint as previous described. Although ball 1030 is contained or trapped within race 1002, ball 1030 can pivot and rotate within race 1002. It is to be understood that slot 1022 and thus race 1002 can be linear and also can be configured in accordance with the various configurations of slot 1022 and linear race 1002 shown in the embodiments of FIGS. 1A-1H. Aperture 1036 of ball 1030 is accessible and configured for mounting adaptive spinal rod 1000 to a bone anchor as shown in FIG. 10B.
  • FIG. 10B, shows a bone anchor 1050 configured for attachment of adaptive spinal rod 1000 to a vertebra. As shown in FIG. 10E, bone anchor 1050 includes a threaded shaft 1052 at the distal end. Threaded shaft 1052 is sized and configured for engaging a vertebra. In preferred embodiments threaded shaft 1052 is sized and configured for implantation in the pedicle of a vertebra. Attached to threaded shaft 1052 is head 1054. Head 1054 includes surface features 1055 which permit head to be engaged by a tool to rotate head 1054 and threaded shaft 1052 and drive bone anchor 1050 into a desired implant location. Protruding proximally from head 1054 is a second mount 1051. Second mount 1051 can be provided with surface texture e.g. knurling and/or surface features. Second mount 1051 is designed to be received in and engaged by connector 1060 of FIGS. 10C-10G. Protruding proximally from second mount 1051 is first mount 1056. First mount 1056 has a smooth exterior surface 1057 to receive ball 1030 of FIG. 10A. Protruding proximally of first mount 1056 is a threaded shaft 1057 for attaching a nut 1059 to secure ball 1030 of FIG. 10A. In the proximal end of threaded shaft 1057 is an aperture 1058. Aperture 1058 is shaped such that the aperture 1058 can be engaged by a driver for implanting/removing bone anchor 1050 and/or attaching nut 1059. For example, aperture 1058 has, in some embodiments, a hexagonal or octagonal cross-section.
  • Referring next to FIG. 10C, which is an exploded view of connector 1060 the connector 1060 revealing the components: snap ring 1002, locking screw 1077, clamp ring 1061, swivel 1070 and plunger 1080. As shown in FIG. 10C, clamp ring 1061 is generally annular with a bore 1069. Bore 1069 of clamp ring 1061 is sized such that the clamp ring 1061 can slide freely up and down second mount 1051 of bone anchor 1050 (see FIG. 10B) and rotate around the second mount 1051 before the clamp ring 1061 is locked. A rim 1063 is, in some embodiments, provided around bore 1069. On one side of clamp ring 1061 is a cylindrical extension 1064. A bore 1062 passes through the middle of cylindrical extension 1064 and intersects with bore 1069 of the clamp ring 1061. Cylindrical extension 1064 has a groove 1068 on its outer surface. The groove 1068 is sized so that snap ring 1002 fits entirely within the groove 1068 when snap ring 1002 is compressed.
  • Referring to FIGS. 10C and 10D (which shows an alternate view of swivel 1070). Connector 1070 has a channel 1074 which passes through swivel 1070 and which is sized to receive therethrough the rod of an adaptive spinal rod (or conventional spinal rod). Swivel 1070 has a threaded aperture 1078 sized to fit locking screw 1077. Threaded aperture 1078 intersects channel 1074 to allow set screw 1077 to contact a spinal rod within channel 1074. An aperture 1071 passes through another side of swivel 1070 and intersects with channel 1074. Aperture 1071 is sized to receive cylindrical extension 1064 of clamp ring 1061 and plunger 1080. Aperture 1071 has a lip 1075 which prevents plunger 1080 from slipping too far into channel 1074. Aperture 1071 also has a groove 1072 sized to engage snap ring 1002.
  • Referring again to FIG. 10C, plunger 1080 is generally cylindrical and sided to fit within bore 1062. The first end 1082 of plunger 1080 is inserted into bore 1062 of clamp ring 1061. First end 1082 is, in some embodiments, concave so as to better engage a bone anchor placed in bore 1069. Plunger 1080 has a lip 1086 at its second end 1084 so that it cannot fall entirely through bore 1062. Snap ring 1002 is designed to fit within groove 1068 of cylindrical extension 1064. In an uncompressed state snap ring 1002 is slightly smaller in diameter to fit over cylindrical extension 1064. To insert snap ring 1002 into groove 1064, snap ring 1002 is expanded slightly and pushed over cylindrical extension 1064 of clamp ring 1061 until snap ring 1002 snaps into groove 1068.
  • During assembly, snap ring 1002 is compressed into groove 1064 of cylindrical extension 1064 while cylindrical extension 1064 is inserted into aperture 1071. When cylindrical extension 1064 is inserted the correct distance into aperture 1071, groove 1068 becomes aligned with groove 1072 and snap ring 1002 can expand into groove 1072. When snap ring 1002 has expanded into groove 1072 a portion of snap ring 1002 remains within each of grooves 1072 and 1068. Cylindrical extension 1064 is thereby locked into aperture 1071 of swivel 1070. Cylindrical extension 1064 can, however, rotate within aperture 1071. Furthermore, plunger 1080 may still slide somewhat in and out of bore 1062 of clamp ring 1061. Second end 1084 of plunger 1080 protrudes slightly into the channel 1074 when assembled as described below. When the plunger 1080 is pushed through bore 1062 outwards from channel 1074 the plunger grips the second mount and prevents the clamp ring 1061 from moving in any direction.
  • FIGS. 10E and 10F illustrate the clamping action of connector 1060 to rod 1010 and to the second mount 1056 of bone anchor 1050. As shown in FIG. 10E, rod 1010 (shown in section) is received in channel 1074 of connector 1060. Second mount 1051 is received in bore 1069 of clamp ring 1061. Plunger 1080 (shown by dotted line) sits in bore 1062 (not shown) of clamp ring 1061 between rod 1010 and second mount 1051. In this unclamped configuration, clamp ring 1061 may slide up and down on second mount 1051 and rotate around second mount 1051; swivel 1070 is free to also free to rotate relative to clamp ring 1061; and rod 1010 can slide freely in and out of channel 1074. The unclamped configuration thereby allows adjustment of the direction and angle of rod 1010 with several degrees of freedom.
  • As shown in FIG. 10F, when set screw 1077 is tightened against a rod 1010 within channel 1074 of swivel 1070, the set screw 1077 pushes rod 1010 against a ramp 1078 at the opposite side of channel 1074 from locking screw 1077. Ramp 1078 pushes rod 1088 against plunger 1080. Plunger 1080 is forced by rod 1010 through bore 1062 (not shown) in clamp ring 1061. Plunger 1080 is thereby forced against second mount 1051 of the bone anchor 1050 preventing further movement of clamp ring 1061 relative to bone anchor 1050. The force of plunger 1080 against second mount 1051 also applies force between grooves 1068 and 1072 and snap ring 1002 (see FIGS. 10C and 10D) thereby preventing further rotation of swivel 1070 relative to clamp ring 1061. Additionally rod 1010 is locked in position within aperture 1074. Operation of the single set screw 1077 serves to place the connector in a clamped configuration and lock the clamp ring 1061 to the second mount 1051 of the bone anchor 1050, lock swivel 1070 in a fixed position relative to clamp ring 1061 and secure rod 1010 within the channel 1074 of connector 1060.
  • The connector 1060 of FIGS. 10C-10F may be used, in some embodiments, to construct an adaptive stabilization assembly for one or more levels of the spine of a patient. FIG. 10G shows an example of a two-level adaptive stabilization assembly 1090 utilizing the connector 1060 of FIGS. 10C-10F. FIG. 10G shows how the components may be assembled and implanted in the spine of a patient to provide a multilevel adaptive stabilization assembly which provides stabilization of the spine and load sharing while preserving motion. Note that an identical or similar construct would preferably be implanted on the left side of the spine.
  • As shown in FIG. 10G, rod 110 of adaptive spinal rod 100 is mounted to head 174 of spinal screw 170. Ball 130 of adaptive spinal rod 100 is secured to bone anchor 1050 by nut 1059. Sliding ball-joint 101 permits bone anchor 1050 to slide, pivot and rotate relative to spinal screw 170. Connector 1060 is also mounted to bone anchor 1050. Set screw 1077 secures clamp ring 1061 of connector to bone anchor 1050 and also secures rod 1010 of adaptive spinal rod 1000 within channel 1074 of swivel 1070. Ball 1030 of adaptive spinal rod 1000 is secured to bone anchor 350 by nut 359. Sliding ball-joint 1001 permits bone anchor 1050 to slide pivot and rotate relative to bone anchor 350. Adaptive spinal prosthesis is typically assembled in vivo by first implanting the bone anchors 1050, 350 and spinal screw 170 in pedicles of adjacent vertebra. After implanting the bone anchors 1050, 350 and spinal screw 170, the connector 1061 is placed over bone anchor 1050 and rod 1010 is positioned within channel 1074 of the connector 1060. Ball 1030 is then secured to bone anchor 350. After securing ball 1030, the position of rod 1010 and swivel 1070 are adjusted and then connector 1060 is locked by tightening set screw 1077.
  • Ball 130 of adaptive spinal rod 100 is secured to bone anchor 1050 by nut 1059. Rod 110 is then placed within head 174 of spinal screw 170. The position of the rod 110 is then adjusted relative to head 174 and the head 174 is secured to rod 110 by set screw 173. Adaptive stabilization assembly 1090 spans two vertebrae two levels of the spine (three vertebrae). Connector 1060 and adaptive spinal rods 100, 1000 permit assembly of adaptive stabilization assembly 1090 for a wide range of different patient anatomies and/or placement of bone anchors 350, 1050 and spinal screw 170. Connector 1060 is particularly useful where, as here, there is slight lateral displacement between the bone anchor positions on either side of a level.
  • Alternative Adaptive Spinal Rods
  • FIGS. 11A-11G are views of an adaptive stabilization system including an alternative adaptive spinal rod according to an embodiment of the present invention. FIG. 11A is an exploded view showing the components of an adaptive spinal rod. FIG. 11B is a perspective view of the assembled adaptive spinal rod. FIG. 11C shows a perspective view of a bone anchor suitable for mounting the adaptive spinal rod to a vertebra. FIG. 11D shows a spinal prosthesis assembly including the adaptive spinal rod, a bone anchor and a conventional pedicle screw. FIGS. 11E, 11F, 11G and 11H are sectional views illustrating the kinematics of the bone anchor relative to the adaptive spinal rod.
  • Referring first to FIG. 11A, which is an exploded view of the components of an adaptive spinal rod 1100. Adaptive spinal rod 1100 has three components: rod 1110, ball or ball-shaped mount or partially-spherical mount 1130 and cap 1140. Rod 1110, preferably, is connected and/or includes at one end to housing 1120. Rod 1110 is similar in size, shape and material to standard spinal rods. Rod 1110 is adapted for mounting to a standard pedicle screw or polyaxial screw (not shown). Rod 1110 is, in preferred embodiments, a cylinder about 5 mm to 6.5 mm in diameter and from 35 mm to 100 mm in length. Housing 1120 is preferably in the form of a flattened disc. Housing 1120 has an aperture 1122 passing therethrough. Aperture 1122 is circular in section to receive ball 1130. Aperture 1122 is shaped to receive ball 1130 from open side 1124. However, the closed side 1126 of aperture 1122 is too small for ball 1130 to pass. Closed side 1126 of aperture 1122 has a curved surface 1128 adapted to engage ball 1130. In one embodiment curved surface 1128 has the same radius of curvature as ball 1130. Open side 1124 of aperture 1122 is shaped to receive cap 1140 after placement of ball 1130. Cap 1140 can be force fit or welded to the housing 1120 to hold ball 1130 in place. In preferred embodiments, rod 1110 and housing 1120 are made in one piece from titanium or titanium alloy.
  • As indicated above, cap 1140 is adapted to fit within aperture 1122 of housing 1120. Cap 1140 has a cap aperture 1142 therethrough. The open side 1144 of cap aperture 1142 is configured to admit a portion of ball 1130. The closed side 1146 of cap aperture 1142 is too small for ball 1130 to pass. The interior of cap aperture 1142 has a curved surface 1148 adapted to engage ball 1130. In one embodiment curved surface 1148 has the same radius of curvature as ball 1130. During assembly, ball 1130 is placed into aperture 1122 of housing 1120. Cap 1140 is then secured into aperture 1122 of housing 1120 trapping or containing ball 1130 between cap 1140 and housing 1120 to form a ball-joint (see FIG. 11E). When assembled, ball 1130 can pivot and rotate within a race created by curved surface 1148 of cap 1140 and curved surface 1128 of housing 1120.
  • Ball 1130 is in the form of a sphere truncated on two opposing sides 1132, 1134. An elongated slot 1136 passes through ball 1130 from side 1132 to side 1134. Elongated slot 1136 is preferably shaped like an oval and/or a rectangle having rounded corners, and/or “race tracks” and/or elliptical. In the preferred embodiment, the walls of slot 1136 are about perpendicular to the truncated opposing sides 1132, 1134. The width (shorter dimension) 1137 of slot 1136 is preferably at least slightly larger than the diameter of the posterior mount 1156 of bone anchor 1150 to be received in the slot 1136 (not shown, but see FIG. 11C). In embodiments, the length (longer dimension) 1139 of slot 1136 is about 1 mm to 5 mm greater than the diameter of the posterior mount 1156 to be received in slot 1136. In preferred embodiments, the length of slot 1136 is about 1 mm to 3 mm greater than the diameter of the posterior mount 1156 to be received in slot 1136. Ball 1130 is adapted to receive a smooth mount 1156 of a bone anchor 1150—the mount 1156 is held in place using a separate nut 1151 (see FIG. 11D). Slot 1136 is elongated to allow a bone anchor to slide (and rotate) in slot 1136 as explained below. Thus, when secured in place, the posterior mount 1156 can slide and rotate within slot 1136. The bone anchor 1150 can slide, rotate and pivot relative to the spinal rod 1110. The ball 1130 can rotate and pivot inside housing 1120 and spinal rod 1100. The range of sliding movement of the mount 1156 is dependent upon the length of the elongated slot 1136.
  • FIG. 11B shows a fully assembled adaptive spinal rod 1100 in which ball 1130 is positioned between cap 1140 and housing 1120. Aperture 1122 of housing 1120 and cap aperture 1142 of cap 1140 cooperate to from a partially-spherical race 1102 in which ball 1130 is contained or trapped. Although ball 1130 is contained or trapped within circular race 1102, ball 1130 can pivot and rotate within circular race 1102 as shown by arrows 1160, 1162. In combination, the surface of ball 1130 and the linear race 1102 form a ball-joint 1101.
  • As shown in FIG. 11B, slot 1136 of ball 1130 is accessible from both sides of the housing 1120 after ball 1130 has been secured between cap 1140 and housing 1120. Slot 1136 of ball 1130 is accessible and configured for mounting adaptive spinal rod 1100 to a bone anchor, for example, the bone anchor shown, in FIG. 11C. The longitudinal axis of slot 1136 is shown in FIG. 11B to be aligned with the longitudinal axis of rod 1110. However, because ball 1130 can rotate within circular race 1102, slot 1136 can be aligned at an angle to, as well as parallel, to the longitudinal axis of rod 1110. As further discussed herein, this arrangement allows the spinal rod 1110 to be out of alignment with the motion of the spine. When the surgical slot 1136 is aligned with the direction of movement of the spine, and slot 1136 can be at an angle with the longitudinal axis of the spinal rod 1110.
  • FIG. 11C shows a bone anchor 1150 configured for attachment of adaptive spinal rod 1100 to a vertebra. As shown in FIG. 11C, bone anchor 1150 includes a threaded shaft 1152 at the distal end. Threaded shaft 1152 is sized and configured for engaging a vertebra. In preferred embodiments, threaded shaft 1152 is sized and configured for implantation in the pedicle of a vertebra. Attached to threaded shaft 1152 is head 1154. Head 1154 includes surface features 1155 which permit head to be engaged by a tool to rotate head 1154 and threaded shaft 1152 and drive bone anchor 1150 into a desired implant location in a vertebra. Protruding proximally from head 1154 is a mount 1156. Mount 1156 has a smooth cylindrical exterior surface 1157 to which ball 1130 of FIGS. 11A and 11B can be mounted. Protruding proximally of mount 1156 are threaded shaft 1159 and key 1158. Threaded shaft 1159 is configured for attachment of a nut 1151 (not shown, but see FIG. 11D) to secure ball 1130 to mount 1156. Key 1158 is shaped such that the key 1158 can be engaged by a driver for implanting bone anchor 1150 and/or attaching ball 1130. For example, key 1158 has, in some embodiments, a hexagonal or octagonal cross-section. At the base of key 1158 is, in some embodiments, a groove which reduces the cross-section of material such that the key 1158 is designed to breakaway when a predetermined amount of torque is applied to key 1158. The breakaway torque is determined by the shape of the groove and the remaining cross-section of material. The breakaway key can thus be used to ensure that the correct amount of torque is applied when securing a nut to threaded shaft 1159.
  • FIG. 11D shows a perspective view of a spinal prosthesis 1104 including adaptive spinal rod 1100 mounted to bone anchor 1150 by a nut 1151. Spinal prosthesis 1104 includes, in this embodiment: adaptive spinal rod 1100 of FIGS. 11A and 11B; bone anchor 1150 of FIG. 11C; and a conventional spinal screw 1170. Spinal screw 1170 is, in some embodiments, a polyaxial pedicle screw. As shown in FIG. 11D, adaptive spinal rod 1100 is secured at one end to conventional spinal screw 1170. Rod 1110 has been secured into a slot 1172 in a head 1174 of spinal screw 1170 by a set screw 1173. Set screw 1173 secures spinal rod 1110 in a fixed position relative to head 1174 and also, in some embodiments, locks the position of head 1174 relative to the threaded screw shaft 1176 of spinal screw 1170. In spinal prosthesis 1104, when implanted, rod 1110 and housing 1120 of adaptive spinal rod 1100 are secured in a fixed position relative to spinal screw 1170 (and any vertebra to which it is mounted).
  • Adaptive spinal rod 1100 is secured, at the other end to bone anchor 1150 of FIG. 11C through ball 1130. Ball 1130, contained or trapped within race 1102, has been secured to posterior mount 1156 of bone anchor 1150. Breakaway key 1158 (see FIG. 11C) has been broken away from posterior mount 1156 during implantation, and removed from the patient. Although ball 1130 has been secured to mount 1156, ball 1130 is still able to pivot and rotate within race 1102 relative to housing 1120 of adaptive spinal rod 1100. Moreover, posterior mount 1156 can still slide and rotate within slot 1136 of ball 1130. It is to be understood that mount 1156 of bone anchor 1150 can slide along the longer dimension 1139 of slot 1136 in ball 1130. Further, if bone anchor 1150 is loosely secured to ball 1150 by nut 1151, bone anchor 1150 can slide through ball 1130 in the directions of sides 1132 and 1134. Consequently, with bone anchor 1150 secured to adaptive spinal rod 1100 through ball 1130 (FIG. 11E), bone anchor 1150 is still able to slide, pivot and rotate relative to rod 1110 and spinal screw 1170. (See FIGS. 11E, 11F, 11G and 11H). Similarly, the spinal rod 1100 can slide, pivot and rotate relative to posterior mount 1156 and also bone anchor 1150 (see FIGS. 11E, 11F, 11G and 11H).
  • Referring again FIG. 11D, pivoting of ball 1130 allows bone anchor 1150 to pivot relative rod 1110 as shown by arrows 1160. In preferred embodiments, bone anchor 1150 can pivot in all directions from perpendicular without interference between housing 1120 and either head 1154 or nut 1151. Head 1154 and nut 1151 are, in some embodiments, provided with relief features to prevent interference with housing 1120. Rotation of ball 1130 allows bone anchor 1150 to rotate around its longitudinal axis relative to rod 1110 as shown by arrow 1162. Such rotation is also permitted by rotation of mount 1156 within slot 1136. Sliding movement of posterior mount 1156 within slot 1136 also allows linear movement of bone anchor 1150 relative to rod 1110 as shown by arrow 1164. This linear movement is shown aligned with the longitudinal axis of rod 1110. However, as previously stated, because ball 1130 can rotate, the longitudinal axis of slot 1136 can align itself at an angle to the longitudinal axis of rod 1110 to better accommodate relative movement of the vertebrae in which bone anchors 1150 and 1170 are implanted.
  • FIGS. 11E, 11F, 11G and 11H are partial sectional views of spinal prosthesis 1104 of FIG. 11D illustrating the kinematics of bone anchor 1150 relative to adaptive spinal rod 1100 in different planes. FIG. 11E shows a section through bone anchor 1150 and adaptive spinal rod 1100 in a substantially saggital plane. FIG. 11F shows a section through bone anchor 1150 and adaptive spinal rod 1100 in a substantially transverse plane. FIGS. 11G and 11H show sections through bone anchor 1150 and adaptive spinal rod 1100 in a substantially dorsal plane through the middle of the housing 1120.
  • Referring first to FIG. 11E shows a section through bone anchor 1150 and adaptive spinal rod 1100 in a substantially saggital plane (vertical and including the longitudinal axis of bone anchor 1150). As shown in FIG. 11E, ball 1130 is contained or trapped between cap 1140 and housing 1120 to form a ball-joint. Ball 1130 can pivot within the housing 1120 within limits imposed by contact between housing 1120, cap 1140, nut 1151 and head 1154. Additionally, posterior mount 1156 can slide within slot 1136 of ball 1130 within limits imposed by contact of posterior mount 1156 and the walls of slot 1136. Additionally, bone anchor 1150 can rotate in slot 1136. As a result, bone anchor 1150 can pivot in the saggital plane as shown by arrow 1182 and translate in the saggital plane as shown by arrow 1186 and rotate. Additionally, if desired, the nut 1151 can be fastened to threaded shaft 1159 in a manner that allows the bone anchor 1150 to translate along the longitudinal axis along the direction of arrow 1187. This can be accomplished by providing for a longer posterior mount 1156 that distances nut 1131 further from the ball 1130 than is shown in FIG. 11G. This arrangement can be provided in the other embodiments discussed herein.
  • In the saggital plane shown in FIG. 11E, slot 1136 allows bone anchor 1150 a limited range of vertical movement which corresponds to spinal flexion/extension (shown by arrow 1186). The desired range of vertical motion 1186, and thus the dimensions of slot 1136, are selected based upon the anatomical and functional needs of a patient. In embodiments, the range of movement is limited to less than 5 mm. In preferred embodiments, the range of translational movement is approximately 2 mm. The difference between the length of slot 1136 and the diameter of posterior mount 1156 controls the linear range of movement. Further, for large patients, the range of motion can be greater than 5 mm.
  • In the saggital plane shown in FIG. 11E, the ball-joint also allows bone anchor 1150 a limited angular range of movement which corresponds to spinal flexion/extension (shown by arrow 1182). The desired range of angular motion 1182, is selected based upon the anatomical and functional needs of a patient. In the embodiments, preferably the range of angular movement in the saggital plane is limited to less than 15 degrees.
  • Referring now to FIG. 11F which shows a section through bone anchor 1150 and adaptive spinal rod 1100 in a substantially transverse plane. In the transverse plane shown in FIG. 11F, the ball-joint 1101 allows bone anchor 1150 a limited angular range of movement which corresponds to spinal rotation (shown by arrow 1184). The range of angular movement is limited by contact between housing 1120 and cap 1140 with nut 1151 and/or head 1154. The desired range of angular motion 1184, and thus the shape of housing 1120, cap 1140, nut 1151 and head 1154 can be selected based upon the anatomical and functional needs of a patient. In the embodiments, preferably the range of angular movement in the transverse plane is limited to less than 10 degrees in each direction. In other embodiments, the range of angular movement can be 10 degrees or greater. The range of angular movement in the transverse plane can, in some embodiments, be different than the range in the saggital/vertical plane.
  • Referring next to FIG. 11G which shows a section through bone anchor 1150 and adaptive spinal rod 1100 in a substantially dorsal plane (vertical and perpendicular to the longitudinal axis of bone anchor 1150). Bone anchor 1150 is oriented either directly into or directly out of the page in this transverse view through housing 1120 and posterior mount 1156. As shown in FIG. 11G, ball 1130 is contained or trapped in housing 1120. Ball 1130 can rotate within race 1202 and thus, in housing 1120. Mount or post 1156 of the bone anchor 1150 is contained or trapped in slot 1136 of ball 1130. Mount or post 1156 of the bone anchor 1150 can slide within slot 1136 as well as rotate within slot 1136. The mount 1156 and thus the bone anchor 1150 can pivot with respect to spinal rod 1100. Based on the embodiment of 11G, the spinal rod 1100 can slide, rotate and pivot relative to the bone anchor 1150. Similarly, the bone anchor 1150 can slide, rotate and pivot relative to the spinal rod 1100, Further, the ball 1130 can rotate and pivot relative to the spinal rod 1100 and the mount or post of the bone anchor can rotate and slide relative to the ball 1130.
  • In the dorsal plane shown in FIG. 11G, linear slot 1136 allows bone anchor 1150 the limited vertical range of movement 1186 as described above. Rotation of ball 1130 within housing 1120 and rotation of posterior mount 1156 within slot 1136 is unrestricted in this preferred embodiment, allowing bone anchor 1150 to rotate freely (360+ degrees) as shown by arrow 1180 which corresponds to lateral spinal twisting. The bone anchor 1150 rotates freely around the longitudinal axis of the spinal rod 1100. The range of rotation 1180 is not limited in this embodiment. However, features to limit such rotation could be designed into one or more of bone anchor 1150, ball 1130, cap 1140, and housing 1120 if desired with appropriate stop surface. The desired range of rotation 1180, can be selected, if necessary or desirable, based upon the anatomical and functional needs of a patient. FIGS. 11H and 11I show other dorsal sectional view. In FIG. 11H, slot 1136 is no longer aligned with the longitudinal axis of rod 1110. FIG. 11H illustrates how the linear movement axis 1188 can change based on rotation of ball 1130.
  • FIG. 11I is a representation of the implantation of two spinal rods 1100 a and 1100 b, side by side in generally a vertical orientation adjacent to the spine of a patient. These respective spinal rods are secured to an upper vertebra with first anchor screws and are secured to lower vertebra with second anchor screws. Due to the placement of the screws and the anatomy of the patient, spinal rod 1100 b is placed about vertical and parallel to the spine. Again, due to the placement of the screws and the anatomy of the patient, spinal rod 1100 a is placed at an angle to vertical and in this embodiment; spinal rod 1100 a is placed at an angle of about 20 degrees or less. The direction of motion of the spine in flexion and extension along a vertical path is shown by arrow 1189. As is evident from FIG. 11I, spinal rod 1100 a is not aligned with vertical arrow 1189. However, as ball 1130 can rotate in housing 1120, slot 1136 can rotate to be substantially parallel with vertical arrow 1189. Thus, the post or mount 1156 located in slot 1136 of spinal rod 1100 a can slide or translate parallel to the direction of motion 1189 of the spine, even though spinal rod 1100 a is not aligned with the direction of motion 1189.
  • With reference to FIGS. 11A to 11H and also to similar embodiments herein, aperture 1122 in the housing of 1120 at the end of spinal rod 1110, instead of being circular as shown, can also be elongated, oval or rectangular with rounded corners, or race-track shaped, as for example, shown in FIGS. 1G and 3A. Accordingly, in this embodiment, both the aperture 1122 in housing 1120 and slot 1136 in mount or ball 1130 are elongated, oval or rectangular with rounded corners or race-track shaped. Accordingly, in addition to the motions afforded between spinal rod 1100 and bone anchor 1150 due to the elongated slot 1136 as shown in FIG. 11G, motions afforded between spinal rod 1100 and bone anchor 1150 due to the elongated aperture 1122 are available in this embodiment.
  • FIGS. 12A-12B are views of an adaptive stabilization system including another alternative adaptive spinal rod according to an embodiment of the present invention. FIG. 12A is an exploded view showing the components of an adaptive spinal rod. FIG. 12B is a plane view of the assembled adaptive spinal rod. FIG. 12C is a perspective view of the adaptive spinal rod 1200 of FIG. 12A as assembled. Referring first to FIG. 12A, which is an exploded view of the components of an adaptive spinal rod 1200, adaptive spinal rod 1200 has three components: rod 1210, ball 1230 and cap 1240. Rod 1210 is preferably connected and/or includes at one end to housing 1220. Rod 1210, preferably, is similar in size, shape and material to standard spinal rods. Rod 1210 is preferably adapted for mounting to a standard pedicle screw or polyaxial screw (not shown). Rod 1210 is, in preferred embodiments, a cylinder about 5 mm to 6.5 mm in diameter and from 35 mm to 100 mm in length.
  • Housing 1220 is preferably in the form of a flattened disc. Housing 1220 has an aperture 1222 passing therethrough. Aperture 1222 is circular in section to receive ball 1230. Aperture 1222 is shaped to receive ball 1230 from open side 1224, however, the closed side 1226 of aperture 1222 is too small for ball 1230 to pass. Closed side 1226 of aperture 1222 has a curved surface 1228 adapted to engage ball 1230. In one embodiment, curved surface 1228 has the same radius of curvature as ball 1230. Open side 1224 of aperture 1222 is shaped to receive cap 1240 after placement of ball 1230. Cap 1240 can be force fit or welded to the housing 1220 to hold ball 1230 in place. In preferred embodiments, rod 1210 and housing 1220 are made in one piece from titanium or titanium alloy.
  • Cap 1240 is adapted to fit within aperture 1222 of housing 1220. Cap 1240 has a cap aperture 1242 therethrough. The open side 1244 of cap aperture 1242 is configured to admit a portion of ball 1230. The closed side 1246 of cap aperture 1242 is too small for ball 1230 to pass. The interior of cap aperture 1242 has a curved surface 1248 adapted to engage ball 1230. In one embodiment curved surface 1248 has the same radius of curvature as ball 1230. During assembly, ball 1230 is placed into aperture 1222 of housing 1220. Cap 1240 is then secured into aperture 1222 of housing 1220 trapping ball 1230 between cap 1240 and housing 1220 to form a ball-joint (see FIG. 12C). When assembled, ball 1230 can pivot and rotate within a race created by curved surface 1248 of cap 1240 and curved surface 1228 of housing 1220.
  • Ball 1230 is in the form of a sphere truncated on two opposing sides 1232, 1234. A bore 1236 passes through ball 1230 from side 1232 to side 1234. The walls of bore 1236 are preferably perpendicular to the truncated opposing sides 1232, 1234. Ball 1230 is adapted to receive a smooth shaft of a bone anchor—the shaft is held in place using a separate nut. The bore 1236 is cylindrical and has an internal diameter sized to receive the posterior shaft of a bone anchor to be received in the bore (not shown but see FIG. 11C) and to allow bone anchor rotation. Thus, when secured in place, the shaft of the bone anchor can slide (along the longitudinal axis of the bone anchor) and rotate within bore 1236. Bore 1236 is eccentric in that the axis of bore 1236 does not pass through the center of ball 1230.
  • FIG. 12B shows an enlarged view of ball 1230 from side 1232. Bore 1236 passes all the way through ball 1230. The axis of bore 1236 is preferably perpendicular to side 1232 (and side 1234, not shown). Bore 1236 is circular and the center axis 1237 of bore 1236 is offset from the center axis 1231 of ball 1230 (the axis passing through the center of ball 1230 perpendicular to sides 1232 and 1234). The offset 1239 is illustrated by a double-headed arrow. In embodiments, the axis of bore 1236 is offset from the center of ball 1230 by preferably 0.5 mm to 2.5 mm. In one preferred embodiment, the axis of bore 1236 is offset from the center of ball 1230 by 1 mm. Because of the offset, rotation of the ball 1230 can move the center axis 1237 of bore 1236 through a range of double the amount of offset 1239. When integrated into adaptive spinal rod 1200, ball 1230 provides a linear range of motion of twice the amount of offset between the rod 1210 and a shaft mounted in bore 1236 achieving results kinematically similar to adaptive spinal rod 1100 of FIGS. 11A-11H.
  • FIG. 12C shows a fully assembled adaptive spinal rod 1200 in which ball 1230 is positioned between cap 1240 and housing 1220. Aperture 1222 of housing 1220 and cap aperture 1242 of cap 1240 cooperate to from a partially-spherical race 1202 in which ball 1230 is contained or trapped. Although ball 1230 is contained or trapped within race 1202, ball 1230 can pivot and rotate within circular race 1202. In combination, the surface of ball 1230, and the linear race 1202 form a ball-joint.
  • As shown in FIG. 12C, bore 1236 of ball 1230 is accessible from both sides of the housing 1220 after ball 1230 has been secured between cap 1240 and housing 1220. Bore 1236 of ball 1230 is accessible and configured for mounting adaptive spinal rod 1200 to a bone anchor, for example, the bone anchor shown, in FIG. 11C. The bore 1236 is shown in FIG. 12B to be on the opposite side of race 1202 from rod 1210. However, because ball 1230 can rotate within race 1202, bore 1236 can move closer to rod 1210 by a distance double the offset 1239 to position 1241 (See FIG. 12B).
  • Materials for Adaptive Spinal Rod
  • Movement of the adaptive spinal rod relative to the bone anchor provides load sharing and adaptive stabilization properties to the adaptive stabilization assembly. The characteristics of the material of the adaptive spinal rod in combination with the dimensions of the components affect the force-deflection characteristics of the adaptive spinal rod. The dimensions and materials may be selected to achieve the desired force-deflection characteristics.
  • The adaptive spinal rod and bone anchors are preferably made of biocompatible implantable metals. Components of the adaptive spinal rod are, in some embodiments, made from stainless steel, titanium, titanium alloy and/or cobalt chrome. In preferred embodiments, the bone anchor and adaptive spinal rod are made of titanium alloy; however, other materials, for example, stainless steel may be used instead of or in addition to the titanium components. Furthermore, moving components of the adaptive spinal rod are, in some embodiments, made of cobalt chrome for good wear characteristics.
  • The particular adaptive stabilization assemblies shown herein are provided by way of example only. It is an aspect of preferred embodiments of the present invention that a range of components be provided and that the components may be assembled in different combinations and organizations to create different assemblies suitable for the functional needs and anatomy of different patients. Also, adaptive spinal rods having different force deflection characteristics may be incorporated at different spinal levels in accordance with the anatomical and functional requirements. Stabilization and load sharing may be provided at one or more motion segments and in some cases stabilization and load sharing may be provided at one or more motion segments in conjunction with fusion at an adjacent motion segment. Particular adaptive stabilization assemblies may incorporate combinations of the bone anchors, adaptive spinal rods, vertical rods, deflection rods, offset and coaxial connectors described herein, described in the related applications incorporated by reference, and also standard spinal stabilization and/or fusion components, for example screws, rods and polyaxial screws.
  • The foregoing description of preferred embodiments of the present invention has been provided for the purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise forms disclosed. Many embodiments were chosen and described in order to best explain the principles of the invention and its practical application, thereby enabling others skilled in the art to understand the invention for various embodiments and with various modifications that are suited to the particular use contemplated. It is intended that the scope of the invention be defined by the claims and their equivalents.

Claims (28)

  1. 1. An adaptive spinal rod adapted to stabilize a spine, wherein the spinal rod comprises:
    an elongated rod having a first end, a second end and a longitudinal rod axis;
    a housing at the first end of the rod;
    a rod bore passing through the housing at an angle with respect to the longitudinal rod axis;
    a linear ball race within the bore;
    a ball-shaped mount contained within the linear ball race; and
    a ball bore passing through the ball-shaped mount and adapted to receive a post whereby the ball-shaped mount is adapted to be secured to a post while allowing the ball-shaped mount to slide, rotate and pivot relative to the elongated rod.
  2. 2. The adaptive spinal rod of claim 1, wherein the spinal rod comprises a cap which forms a part of the linear ball race and secures the ball-shaped mount within the linear ball race.
  3. 3. The adaptive spinal rod of claim 2, wherein the cap is mounted in the rod-bore.
  4. 4. The adaptive spinal rod of claim 1, wherein the ball bore is threaded and adapted to secure the ball-shaped mount to a threaded post of a bone anchor.
  5. 5. The adaptive spinal rod of claim 4, wherein the ball-shaped mount has a tool engagement feature which is adapted to permit the ball-shaped mount to engage and be turned by a tool to secure the ball bore to a threaded post of a bone anchor.
  6. 6. The adaptive spinal rod of claim 1, wherein the ball-shaped mount comprises cobalt chrome.
  7. 7. The adaptive spinal rod of claim 1, in combination with a bone anchor, wherein:
    the bone anchor comprises a threaded shaft adapted to engage a vertebra and a post that can mount ball-shaped mount.
  8. 8. The adaptive spinal rod of claim 1, further comprising:
    a second ball-shaped mount contained within the linear ball race; and
    a second ball bore passing through the ball-shaped mount and adapted to receive a post whereby the second ball-shaped mount is adapted to be secured to a post while allowing the second ball-shaped mount to slide and pivot relative to the post.
  9. 9. The adaptive spinal rod of claim 1, wherein the linear ball race has an adjustable length.
  10. 10. The adaptive spinal rod of claim 1 wherein said rod passes through the housing about perpendicular to the elongated rod axis.
  11. 11. The adaptive spinal rod of claim 1 wherein said elongated rod is adapted to slide, rotate and pivot relative to the post.
  12. 12. The adaptive spinal rod of claim 1 wherein said ball-shaped mount is adapted to secure a post substantially perpendicular to the elongated rod axis while allowing the rod to slide, rotate and pivot relative to the post.
  13. 13. The adaptive spinal rod of claim 1, wherein the linear ball race is parallel to and off-set from said longitudinal rod axis.
  14. 14. The adaptive spinal rod of claim 1 wherein said ball bore is adapted to allow the post to slide through the ball bore.
  15. 15. The adaptive spinal rod of claim 1 wherein said ball bore is off-set from the center of said ball-shaped mount.
  16. 16. The adaptive spinal rod of claim 1 wherein said rod bore is one of oval, elliptical, rectangular with rounded corners and race-track shaped.
  17. 17. An adaptive spinal rod adapted to span at least about a spinal segment, wherein the spinal rod comprises:
    an elongated rod having a first end, a second end, and a longitudinal rod axis;
    an elongated race located at the first end of the rod;
    a mount contained by the race;
    the mount having a bore adapted to receive a post from a bone anchor; and
    wherein said mount can slide, rotate and pivot relative to the elongated rod.
  18. 18. (canceled)
  19. 19. The adaptive spinal rod of claim 17, wherein said mount is spherically shaped and said elongated rod is adapted to slide, rotate and pivot relative to the bone anchor.
  20. 20. The adaptive spinal rod of claim 17, wherein said race is linear.
  21. 21. The adaptive spinal rod of claim 17, wherein said race has concave sides.
  22. 22. The adaptive spinal rod of claim 17, wherein said mount includes a first curved surface and a second curved surface, with the first curved surface facing the second curved surface.
  23. 23. The adaptive spinal rod of claim 17, wherein said race has convex sides.
  24. 24. The adaptive spinal rod of claim 17 wherein said bore is adapted to allow the post to slide through said bore.
  25. 25. The adaptive spinal rod of claim 17, wherein the elongated race is parallel to and off-set from said longitudinal rod axis.
  26. 26. The adaptive spinal rod of claim 17 wherein said bore is off-set from the center of said curved mount.
  27. 27. The adaptive spinal rod of claim 17 wherein said race is one of oval, elliptical, rectangular with rounded corners, and race-track shaped.
  28. 28. An adaptive spinal rod adapted to span at least about a spinal segment, wherein the spinal rod comprises:
    an elongated rod having a first end, a second end, and a longitudinal rod axis;
    an elongated slot located at the first end of the rod;
    said elongated slot being one of oval, elliptical, rectangular with rounded corners and race-track shaped;
    a curved mount contained by the slot;
    the curved mount having a bore adapted to receive a post from a bone anchor; and
    wherein said curved mount can slide, rotate and pivot relative to the elongated slot.
US13014878 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine Abandoned US20110307018A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US35350810 true 2010-06-10 2010-06-10
US201161435961 true 2011-01-25 2011-01-25
US13014878 US20110307018A1 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US13014878 US20110307018A1 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine
PCT/US2011/039144 WO2011156236A3 (en) 2010-06-10 2011-06-03 Adaptive spinal rod and methods for stabilization of the spine

Publications (1)

Publication Number Publication Date
US20110307018A1 true true US20110307018A1 (en) 2011-12-15

Family

ID=45096835

Family Applications (3)

Application Number Title Priority Date Filing Date
US13014878 Abandoned US20110307018A1 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine
US13014894 Abandoned US20110307015A1 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine
US13014868 Active 2031-10-19 US8518085B2 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine

Family Applications After (2)

Application Number Title Priority Date Filing Date
US13014894 Abandoned US20110307015A1 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine
US13014868 Active 2031-10-19 US8518085B2 (en) 2010-06-10 2011-01-27 Adaptive spinal rod and methods for stabilization of the spine

Country Status (2)

Country Link
US (3) US20110307018A1 (en)
WO (1) WO2011156236A3 (en)

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120029570A1 (en) * 2010-07-29 2012-02-02 Clariance Facet arthroplasty device
US8337532B1 (en) * 2011-12-08 2012-12-25 Spine Wave, Inc. Methods for percutaneously extending an existing spinal construct
US20130013004A1 (en) * 2011-03-09 2013-01-10 Zimmer Spine, Inc. Polyaxial pedicle screw with increased angulation
US20130053848A1 (en) * 2008-06-24 2013-02-28 Extremity Medical, Llc Fixation system, an intramedullary fixation assembly and method of use
US20130085534A1 (en) * 2011-09-30 2013-04-04 Nicolas Hainard Connectors for a secondary bone anchor
US20130172889A1 (en) * 2008-06-24 2013-07-04 Extremity Medical, Llc Fixation system, an intramedullary fixation assembly and method of use
US20130345755A1 (en) * 2012-06-21 2013-12-26 Aesculap Implant Systems, Llc Low profile bone stabilization systems
US20140052189A1 (en) * 2012-08-15 2014-02-20 Blackstone Medical, Inc. Pivoting spinal fixation devices
US20140074169A1 (en) * 2012-09-13 2014-03-13 Warsaw Orthopedic, Inc. Spinal correction system and method

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8900270B2 (en) * 2004-02-17 2014-12-02 Gmedelaware 2 Llc Facet joint replacement instruments and methods
US9579126B2 (en) 2008-02-02 2017-02-28 Globus Medical, Inc. Spinal rod link reducer
US8758411B1 (en) 2011-10-25 2014-06-24 Nuvasive, Inc. Implants and methods for treating spinal disorders
US9757158B2 (en) 2012-12-06 2017-09-12 In Queue Innovations, Llc Minimally invasive spinal column realignment system and method
US20150094769A1 (en) 2013-10-01 2015-04-02 Hamid Abbasi System and method for lengthening an existing spinal support structure
WO2015081027A1 (en) * 2013-11-29 2015-06-04 The Johns Hopkins University Patient-specific trackable cutting guides
FR3027207A1 (en) * 2014-10-15 2016-04-22 Medicrea Int of vertebral osteosynthesis material
FR3027208B1 (en) * 2014-10-15 2016-12-23 Medicrea Int of vertebral osteosynthesis material
CN104323851A (en) * 2014-10-30 2015-02-04 哈尔滨医科大学 Internal fixing device of spine
US20180125533A1 (en) * 2015-04-17 2018-05-10 Apifix Ltd. Expandable polyaxial spinal system
US9980755B2 (en) * 2016-03-29 2018-05-29 Globus Medical, Inc. Revision connectors, systems, and methods thereof

Citations (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4566677A (en) * 1982-06-11 1986-01-28 Vibrachoc Vibration damper and in particular frequency adapter for a helicopter blade
US5129899A (en) * 1991-03-27 1992-07-14 Smith & Nephew Richards Inc. Bone fixation apparatus
US5569246A (en) * 1993-12-28 1996-10-29 Asahi Kogaku Kogyo Kabushiki Kaisha Fixing instrument for spinal fusion members
US20050113927A1 (en) * 2003-11-25 2005-05-26 Malek Michel H. Spinal stabilization systems
US20050131406A1 (en) * 2003-12-15 2005-06-16 Archus Orthopedics, Inc. Polyaxial adjustment of facet joint prostheses
US20050143737A1 (en) * 2003-12-31 2005-06-30 John Pafford Dynamic spinal stabilization system
US20050171543A1 (en) * 2003-05-02 2005-08-04 Timm Jens P. Spine stabilization systems and associated devices, assemblies and methods
US20060052786A1 (en) * 2004-08-17 2006-03-09 Zimmer Spine, Inc. Polyaxial device for spine stabilization during osteosynthesis
US20060149234A1 (en) * 2004-12-22 2006-07-06 Stryker Spine Variable offset connectors and bone fixation methods
US20070093817A1 (en) * 2005-09-29 2007-04-26 Michael Barrus Spinal fixation system having locking and unlocking devices for use with a multi-planar, taper lock screw
US20090016808A1 (en) * 2004-09-03 2009-01-15 Oshkosh Truck Corporation Joint
US20090171395A1 (en) * 2007-12-28 2009-07-02 Jeon Dong M Dynamic spinal rod system
US7744635B2 (en) * 2004-06-09 2010-06-29 Spinal Generations, Llc Spinal fixation system
US7963978B2 (en) * 2007-06-05 2011-06-21 Spartek Medical, Inc. Method for implanting a deflection rod system and customizing the deflection rod system for a particular patient need for dynamic stabilization and motion preservation spinal implantation system
US8057517B2 (en) * 2008-02-26 2011-11-15 Spartek Medical, Inc. Load-sharing component having a deflectable post and centering spring and method for dynamic stabilization of the spine
US8313515B2 (en) * 2007-06-15 2012-11-20 Rachiotek, Llc Multi-level spinal stabilization system

Family Cites Families (520)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB780652A (en) 1954-04-30 1957-08-07 Zimmer Orthopaedic Ltd Improvements in or relating to apparatus for use in spinal fixation
JPS52130183A (en) 1975-04-22 1977-11-01 Ingubuaru Buranemaruku Peru Method of forming bone setting
GB1551706A (en) 1975-04-28 1979-08-30 Downs Surgical Ltd Surgical implant
DE2649042C2 (en) 1976-10-28 1978-09-07 Max Bernhard 7900 Ulm Ulrich
US4274401A (en) 1978-12-08 1981-06-23 Miskew Don B W Apparatus for correcting spinal deformities and method for using
US4411259A (en) 1980-02-04 1983-10-25 Drummond Denis S Apparatus for engaging a hook assembly to a spinal column
US4409968A (en) 1980-02-04 1983-10-18 Drummond Denis S Method and apparatus for engaging a hook assembly to a spinal column
US4347845A (en) 1981-03-23 1982-09-07 Mayfield Jack K Hook inserter device
US4567885A (en) 1981-11-03 1986-02-04 Androphy Gary W Triplanar knee resection system
US4422451A (en) 1982-03-22 1983-12-27 Ali Kalamchi Spinal compression and distraction instrumentation
US4479491A (en) 1982-07-26 1984-10-30 Martin Felix M Intervertebral stabilization implant
DE3306657C2 (en) 1983-02-25 1986-12-11 Fa. Heinrich C. Ulrich, 7900 Ulm, De
FR2545350B1 (en) 1983-05-04 1985-08-23 Cotrel Yves Apparatus for shoring spine
US4611580A (en) 1983-11-23 1986-09-16 Henry Ford Hospital Intervertebral body stabilization
US4696290A (en) 1983-12-16 1987-09-29 Acromed Corporation Apparatus for straightening spinal columns
US4611581A (en) 1983-12-16 1986-09-16 Acromed Corporation Apparatus for straightening spinal columns
US4611582A (en) 1983-12-27 1986-09-16 Wisconsin Alumni Research Foundation Vertebral clamp
GB2173104B (en) 1984-02-28 1987-11-25 Peter John Webb Spinal fixation apparatus
US4604995A (en) 1984-03-30 1986-08-12 Stephens David C Spinal stabilizer
CA1227902A (en) 1984-04-02 1987-10-13 Raymond G. Tronzo Fenestrated hip screw and method of augmented internal fixation
US4573454A (en) 1984-05-17 1986-03-04 Hoffman Gregory A Spinal fixation apparatus
US4655199A (en) 1985-03-29 1987-04-07 Acromed Corporation Spinal column straightening apparatus
US4743260A (en) 1985-06-10 1988-05-10 Burton Charles V Method for a flexible stabilization system for a vertebral column
US4653481A (en) 1985-07-24 1987-03-31 Howland Robert S Advanced spine fixation system and method
US4773402A (en) 1985-09-13 1988-09-27 Isola Implants, Inc. Dorsal transacral surgical implant
US4648388B1 (en) 1985-11-01 1995-10-31 Acromed Corp Apparatus and method for maintaining vertebrae in a desired relationship
US4719905B1 (en) 1985-11-01 1995-10-31 Acromed Corp Apparatus and method for maintaining vertebrae in a desired relationship
DE3614101C1 (en) 1986-04-25 1987-10-22 Juergen Prof Dr Med Harms pedicle screw
US4805602A (en) 1986-11-03 1989-02-21 Danninger Medical Technology Transpedicular screw and rod system
DE3639810C2 (en) 1986-11-21 1998-04-09 Heinrich Ulrich Implant for spinal correction and / or stabilization
FR2612070B1 (en) 1987-03-12 1992-09-18 Privat Jean Marie Posterior spinal osteosynthesis device
FR2615095B1 (en) 1987-05-15 1989-08-18 Fabrication Materiel Orthopedi Osteosynthesis instrumentation for the correction of scoliosis by posterior lumbar path
DE3800052A1 (en) 1987-07-08 1989-07-13 Harms Juergen positioning screw
US4913134A (en) 1987-07-24 1990-04-03 Biotechnology, Inc. Spinal fixation system
US4887595A (en) 1987-07-29 1989-12-19 Acromed Corporation Surgically implantable device for spinal columns
US4950269A (en) 1988-06-13 1990-08-21 Acromed Corporation Spinal column fixation device
FR2633177B1 (en) 1988-06-24 1991-03-08 Fabrication Materiel Orthopedi Implant for spinal osteosynthesis device, in particular trauma
US4955885A (en) 1988-12-21 1990-09-11 Zimmer, Inc. Surgical slider instrument and method of using instrument
US5147359A (en) 1988-12-21 1992-09-15 Zimmer, Inc. Spinal hook body
US5201734A (en) 1988-12-21 1993-04-13 Zimmer, Inc. Spinal locking sleeve assembly
US5116334A (en) 1988-12-21 1992-05-26 Zimmer, Inc. Posterior spinal system and method
GB2254394B (en) 1988-12-21 1993-03-17 Squibb Bristol Myers Co Coupler assembly
US5074864A (en) 1988-12-21 1991-12-24 Zimmer, Inc. Clamp assembly for use in a spinal system
US5112332A (en) 1988-12-21 1992-05-12 Zimmer, Inc. Method of performing spinal surgery
FR2642645B1 (en) 1989-02-03 1992-08-14 Breard Francis flexible intervertebral stabilizer as well as process and apparatus for the control of its tension before installation on the rachis
USRE36221E (en) 1989-02-03 1999-06-01 Breard; Francis Henri Flexible inter-vertebral stabilizer as well as process and apparatus for determining or verifying its tension before installation on the spinal column
US5084049A (en) 1989-02-08 1992-01-28 Acromed Corporation Transverse connector for spinal column corrective devices
US5024213A (en) 1989-02-08 1991-06-18 Acromed Corporation Connector for a corrective device
FR2642643B1 (en) 1989-02-09 1991-05-10 Vignaud Jean Louis spinal instrumentation for universal pedicle fixation screw pitch micrometric adjustment
CA2035348C (en) 1990-02-08 2000-05-16 Jean-Louis Vignaud Adjustable fastening device with spinal osteosynthesis rods
US4987892A (en) 1989-04-04 1991-01-29 Krag Martin H Spinal fixation device
FR2645732B1 (en) 1989-04-13 1997-01-03 Cotrel Yves Vertebral implant for osteosynthesis device
DE3923996C2 (en) 1989-07-20 1993-08-26 Lutz 7730 Villingen-Schwenningen De Biedermann
US5261913A (en) 1989-07-26 1993-11-16 J.B.S. Limited Company Device for straightening, securing, compressing and elongating the spinal column
US5344422A (en) 1989-10-30 1994-09-06 Synthes (U.S.A.) Pedicular screw clamp
FR2659225B1 (en) 1990-03-08 1995-09-08 Sofamor Transverse fixing device to ensure a rigid transverse connection between two rods of a spinal osteosynthesis system.
US5030220A (en) 1990-03-29 1991-07-09 Advanced Spine Fixation Systems Incorporated Spine fixation system
WO1991016020A1 (en) 1990-04-26 1991-10-31 Danninger Medical Technology, Inc. Transpedicular screw system and method of use
US5290289A (en) 1990-05-22 1994-03-01 Sanders Albert E Nitinol spinal instrumentation and method for surgically treating scoliosis
US5102412A (en) 1990-06-19 1992-04-07 Chaim Rogozinski System for instrumentation of the spine in the treatment of spinal deformities
US5129900B1 (en) 1990-07-24 1998-12-29 Acromed Corp Spinal column retaining method and apparatus
FR2666981B1 (en) 1990-09-21 1993-06-25 Commarmond Jacques Synthetic vertebral ligament.
US5127912A (en) 1990-10-05 1992-07-07 R. Charles Ray Sacral implant system
US6520990B1 (en) 1990-10-05 2003-02-18 Sdgi Holdings, Inc. Lateral fixation plates for a spinal system
US5300073A (en) 1990-10-05 1994-04-05 Salut, Ltd. Sacral implant system
US5113685A (en) 1991-01-28 1992-05-19 Acromed Corporation Apparatus for contouring spine plates and/or rods
FR2672202B1 (en) 1991-02-05 1993-07-30 Safir bone surgical implant, particularly for inter-vertebral stabilizer.
FR2676911B1 (en) 1991-05-30 1998-03-06 Psi Ste Civile Particuliere Device intervertebral stabilization dampers.
US5261911A (en) 1991-06-18 1993-11-16 Allen Carl Anterolateral spinal fixation system
FR2680461B1 (en) 1991-08-19 1993-11-26 Fabrication Mat Orthopedique Including osteosynthesis implant device for the spine and corresponding device for its implementation.
US5257993A (en) 1991-10-04 1993-11-02 Acromed Corporation Top-entry rod retainer
NL9200288A (en) 1992-02-17 1993-09-16 Acromed Bv A device for fixation of at least a portion of the cervical and / or thoracic vertebral column of the human being.
JP2664614B2 (en) 1992-02-20 1997-10-15 ジ・ベ・エス ソシエテ アノニム Correction of the cervical spine, fixed, tightening and traction device
DE9202745U1 (en) 1992-03-02 1992-06-11 Howmedica Gmbh, 2314 Schoenkirchen, De
US5171279A (en) 1992-03-17 1992-12-15 Danek Medical Method for subcutaneous suprafascial pedicular internal fixation
EP0572790B1 (en) 1992-06-04 1996-02-14 Synthes AG, Chur Osteosynthesis anchoring element
US6077262A (en) 1993-06-04 2000-06-20 Synthes (U.S.A.) Posterior spinal implant
US6344057B1 (en) 1994-11-22 2002-02-05 Sdgi Holdings, Inc. Adjustable vertebral body replacement
ES2100348T3 (en) 1992-06-25 1997-06-16 Synthes Ag Osteosynthetic fixation device.
US5281222A (en) 1992-06-30 1994-01-25 Zimmer, Inc. Spinal implant system
US5498264A (en) 1992-07-21 1996-03-12 Synthes (U.S.A.) Clamp connection for connecting two construction components for a setting device, particularly an osteosynthetic setting device
US5397363A (en) 1992-08-11 1995-03-14 Gelbard; Steven D. Spinal stabilization implant system
ES2099326T3 (en) 1992-08-12 1997-05-16 Synthes Ag Spinal fixation element.
GB9217578D0 (en) 1992-08-19 1992-09-30 Surgicarft Ltd Surgical implants,etc
US5382248A (en) 1992-09-10 1995-01-17 H. D. Medical, Inc. System and method for stabilizing bone segments
FR2697742B1 (en) 1992-11-06 1994-12-16 Biomat An osteosynthesis device for spinal consolidation.
US5562735A (en) 1992-11-09 1996-10-08 Hospital For Joint Diseases Spinal stabilization system and improved method
US5702395A (en) 1992-11-10 1997-12-30 Sofamor S.N.C. Spine osteosynthesis instrumentation for an anterior approach
US5611354A (en) 1992-11-12 1997-03-18 Alleyne; Neville Cardiac protection device
DE4243951C2 (en) 1992-12-23 1997-07-03 Plus Endoprothetik Ag Device for stiffening of a group consisting of at least two vertebrae spine portion
CA2103200A1 (en) 1992-12-28 1994-06-29 Robert S. Howland Cervical spine rod fixation system
US5498262A (en) * 1992-12-31 1996-03-12 Bryan; Donald W. Spinal fixation apparatus and method
US5947965A (en) 1992-12-31 1999-09-07 Bryan; Donald W. Spinal fixation apparatus and method
US5527314A (en) 1993-01-04 1996-06-18 Danek Medical, Inc. Spinal fixation system
US5282801A (en) 1993-02-17 1994-02-01 Danek Medical, Inc. Top tightening clamp assembly for a spinal fixation system
US5549607A (en) 1993-02-19 1996-08-27 Alphatec Manufacturing, Inc, Apparatus for spinal fixation system
DE4307576C1 (en) 1993-03-10 1994-04-21 Biedermann Motech Gmbh Bone screw esp. for spinal column correction - has U=shaped holder section for receiving straight or bent rod
US5415661A (en) 1993-03-24 1995-05-16 University Of Miami Implantable spinal assist device
FR2704133B1 (en) 1993-04-19 1995-07-13 Stryker Corp Implant for osteosynthesis device in particular of the spine.
FR2704134B1 (en) 1993-04-20 1998-08-28 Stryker Corp Fitting piece for disposifit of osteosynthesis.
ES2115767T3 (en) 1993-05-11 1998-07-01 Synthes Ag Mounting for osteosynthesis and loose gear.
FR2705226B1 (en) 1993-05-17 1995-07-07 Tornier Sa Spinal fixator for holding a spine.
DE4417629B4 (en) 1993-06-24 2006-03-16 SDGI Holdings, Inc., Wilmington Implant for the replacement of vertebral bodies
US5584831A (en) 1993-07-09 1996-12-17 September 28, Inc. Spinal fixation device and method
US5437670A (en) 1993-08-19 1995-08-01 Danek Medical, Inc. Attachment plate for top-tightening clamp assembly in a spinal fixation system
FR2709246B1 (en) 1993-08-27 1995-09-29 Martin Jean Raymond dynamic spinal orthosis implanted.
CA2150797C (en) 1993-10-08 2011-07-05 Chaim Rogozinski Spinal treatment and long bone fixation apparatus and method
US6379354B1 (en) 1993-10-08 2002-04-30 Chaim Rogozinski Spinal implant and method
US5380326A (en) 1993-11-12 1995-01-10 Lin; Chih-I Clamping device for vertebral locking rod
FR2712481B1 (en) 1993-11-18 1996-01-12 Graf Henry Improvements to flexible inter-vertebral stabilizers.
US5466237A (en) 1993-11-19 1995-11-14 Cross Medical Products, Inc. Variable locking stabilizer anchor seat and screw
US5628740A (en) 1993-12-23 1997-05-13 Mullane; Thomas S. Articulating toggle bolt bone screw
US5611800A (en) 1994-02-15 1997-03-18 Alphatec Manufacturing, Inc. Spinal fixation system
DE59408313D1 (en) 1994-02-28 1999-07-01 Sulzer Orthopaedie Ag Stabilization of adjacent vertebrae
US5601552A (en) 1994-03-18 1997-02-11 Sofamor, S.N.C. Fixing device for a rigid transverse connection device between rods of a spinal osteosynthesis system
WO1998008454A1 (en) 1994-05-25 1998-03-05 Jackson Roger P Apparatus and method for spinal fixation and correction of spinal deformities
FR2721501B1 (en) 1994-06-24 1996-08-23 Fairant Paulette Prosthetic vertebral facet joints.
DE59409553D1 (en) 1994-06-30 2000-11-23 Sulzer Orthopaedie Ag Baar Device for connecting vertebrae
DE4425357C2 (en) 1994-07-18 1996-07-04 Harms Juergen anchoring element
US5961517A (en) 1994-07-18 1999-10-05 Biedermann; Lutz Anchoring member and adjustment tool therefor
US5681310A (en) 1994-07-20 1997-10-28 Yuan; Hansen A. Vertebral auxiliary fixation device having holding capability
FR2722980B1 (en) 1994-07-26 1996-09-27 Samani Jacques inter-vertebral implant thorny
US5681311A (en) 1994-09-15 1997-10-28 Smith & Nephew, Inc. Osteosynthesis apparatus
US5690633A (en) 1994-09-23 1997-11-25 Smith & Nephew Richards, Inc. Orthopedic fracture fixation device
US6004322A (en) 1994-10-25 1999-12-21 Sdgi Holdings, Inc. Modular pedicle screw system
FR2726171B1 (en) 1994-10-28 1997-01-24 Jbs Sa A rehabitable connecting screw for bone joint, intended in particular for stabilization of at least two vertebrae
DE69526113D1 (en) 1994-11-16 2002-05-02 Advanced Spine Fixation Syst Griffin hook for fixation of spinal segments
US5716358A (en) 1994-12-02 1998-02-10 Johnson & Johnson Professional, Inc. Directional bone fixation device
FR2729556B1 (en) 1995-01-23 1998-10-16 Sofamor Spinal osteosynthesis device has median hook and anchor support vertebral
US5620443A (en) * 1995-01-25 1997-04-15 Danek Medical, Inc. Anterior screw-rod connector
US5643260A (en) 1995-02-14 1997-07-01 Smith & Nephew, Inc. Orthopedic fixation system
DE19507141B4 (en) 1995-03-01 2004-12-23 Lutz Biedermann Locking
DE19509332C1 (en) 1995-03-15 1996-08-14 Harms Juergen anchoring element
US5562661A (en) * 1995-03-16 1996-10-08 Alphatec Manufacturing Incorporated Top tightening bone fixation apparatus
DE19511268A1 (en) 1995-03-27 1996-10-02 Johannes Franz Dr Med Hoenig Osteosynthesis plate for bone stabilising e.g. post-tumour resection etc.
US5591166A (en) 1995-03-27 1997-01-07 Smith & Nephew Richards, Inc. Multi angle bone bolt
US5688272A (en) 1995-03-30 1997-11-18 Danek Medical, Inc. Top-tightening transverse connector for a spinal fixation system
US5716355A (en) 1995-04-10 1998-02-10 Sofamor Danek Group, Inc. Transverse connection for spinal rods
US5545167A (en) 1995-04-11 1996-08-13 Lin; Chih-I Retaining mechanism of vertebral fixation rod
US5630816A (en) 1995-05-01 1997-05-20 Kambin; Parviz Double barrel spinal fixation system and method
FR2734147B1 (en) 1995-05-19 1997-10-10 Klein Jean Michel An implantable osteosynthesis
JP3689146B2 (en) 1995-05-30 2005-08-31 ペンタックス株式会社 Screw fixing element to the bone
EP0874594B1 (en) 1995-06-06 2003-10-08 SDGI Holdings, Inc. Device for linking adjacent rods in spinal instrumentation
US5683391A (en) 1995-06-07 1997-11-04 Danek Medical, Inc. Anterior spinal instrumentation and method for implantation and revision
US5676665A (en) 1995-06-23 1997-10-14 Bryan; Donald W. Spinal fixation apparatus and method
US5609593A (en) 1995-07-13 1997-03-11 Fastenetix, Llc Advanced polyaxial locking hook and coupling element device for use with top loading rod fixation devices
US5702392A (en) 1995-09-25 1997-12-30 Wu; Shing-Sheng Coupling plate for spinal correction and a correction device of using the same
US6273914B1 (en) 1995-09-28 2001-08-14 Sparta, Inc. Spinal implant
US5683392A (en) 1995-10-17 1997-11-04 Wright Medical Technology, Inc. Multi-planar locking mechanism for bone fixation
US5697929A (en) 1995-10-18 1997-12-16 Cross Medical Products, Inc. Self-limiting set screw for use with spinal implant systems
US5693053A (en) 1995-10-19 1997-12-02 Sdgi Holdings, Inc. Variable angle and transitional linking member
US5688273A (en) 1995-10-23 1997-11-18 Fastenetix, Llc. Spinal implant apparatus having a single central rod and plow hooks
US5690632A (en) 1995-11-30 1997-11-25 Schwartz; Paul Steven Osteosynthesis screw fastener having angularly adjustable threads and methods of use therefor
US5667507A (en) 1995-12-04 1997-09-16 Fastenetix, Llc Compression locking variable length cross-link device for use with dual rod apparatus
WO1997023170A1 (en) 1995-12-22 1997-07-03 Ohio Medical Instrument Company, Inc. Spinal fixation device with laterally attachable connectors
US5669910A (en) 1996-01-02 1997-09-23 Pioneer Laboratories, Inc. Crosslink for implantable rods
FR2743712B1 (en) 1996-01-19 1998-04-30 Louis Rene Device for osteosynthesis of posterior vertebral anchor
US5690629A (en) 1996-04-24 1997-11-25 Acromed Corporation Apparatus for maintaining vertebrae of a spinal column in a desired spatial relationship
FR2748387B1 (en) * 1996-05-13 1998-10-30 Stryker France Sa A bone fastener, in particular the sacrum, in spinal osteosynthesis
US5702399A (en) 1996-05-16 1997-12-30 Pioneer Laboratories, Inc. Surgical cable screw connector
US5713900A (en) 1996-05-31 1998-02-03 Acromed Corporation Apparatus for retaining bone portions in a desired spatial relationship
US6193720B1 (en) 1998-11-30 2001-02-27 Depuy Orthopaedics, Inc. Cervical spine stabilization method and system
US5843082A (en) 1996-05-31 1998-12-01 Acromed Corporation Cervical spine stabilization method and system
US5879350A (en) 1996-09-24 1999-03-09 Sdgi Holdings, Inc. Multi-axial bone screw assembly
US5797911A (en) 1996-09-24 1998-08-25 Sdgi Holdings, Inc. Multi-axial bone screw assembly
US5885286A (en) 1996-09-24 1999-03-23 Sdgi Holdings, Inc. Multi-axial bone screw assembly
US5800435A (en) 1996-10-09 1998-09-01 Techsys, Llc Modular spinal plate for use with modular polyaxial locking pedicle screws
US5735851A (en) 1996-10-09 1998-04-07 Third Millennium Engineering, Llc Modular polyaxial locking pedicle screw
US5964760A (en) 1996-10-18 1999-10-12 Spinal Innovations Spinal implant fixation assembly
US6171311B1 (en) 1996-10-18 2001-01-09 Marc Richelsoph Transverse connector
US5863293A (en) 1996-10-18 1999-01-26 Spinal Innovations Spinal implant fixation assembly
US6416515B1 (en) 1996-10-24 2002-07-09 Spinal Concepts, Inc. Spinal fixation system
US5728098A (en) 1996-11-07 1998-03-17 Sdgi Holdings, Inc. Multi-angle bone screw assembly using shape-memory technology
US5720751A (en) 1996-11-27 1998-02-24 Jackson; Roger P. Tools for use in seating spinal rods in open ended implants
US6485494B1 (en) 1996-12-20 2002-11-26 Thomas T. Haider Pedicle screw system for osteosynthesis
US5683393A (en) 1996-12-23 1997-11-04 Third Millennium Engineering, Llc Bidirectional rod-hook locking mechanism
US5776135A (en) 1996-12-23 1998-07-07 Third Millennium Engineering, Llc Side mounted polyaxial pedicle screw
US6001098A (en) 1997-01-17 1999-12-14 Howmedica Gmbh Connecting element for spinal stabilizing system
EP0954247B1 (en) 1997-01-22 2005-11-23 Synthes Ag Device for connecting a longitudinal bar to a pedicle screw
US5713904A (en) 1997-02-12 1998-02-03 Third Millennium Engineering, Llc Selectively expandable sacral fixation screw-sleeve device
US5752957A (en) 1997-02-12 1998-05-19 Third Millennium Engineering, Llc Polyaxial mechanism for use with orthopaedic implant devices
US5725528A (en) 1997-02-12 1998-03-10 Third Millennium Engineering, Llc Modular polyaxial locking pedicle screw
US5733286A (en) 1997-02-12 1998-03-31 Third Millennium Engineering, Llc Rod securing polyaxial locking screw and coupling element assembly
JP2001527437A (en) 1997-03-07 2001-12-25 グローバーマン、オレン System for percutaneous bone and spinal stabilization, fixation and repair
FR2762986B1 (en) 1997-05-07 1999-09-24 Aesculap Jbs System for spinal osteosynthesis for arthrodesis
US6413257B1 (en) 1997-05-15 2002-07-02 Surgical Dynamics, Inc. Clamping connector for spinal fixation systems
US5785711A (en) 1997-05-15 1998-07-28 Third Millennium Engineering, Llc Polyaxial pedicle screw having a through bar clamp locking mechanism
US5810819A (en) 1997-05-15 1998-09-22 Spinal Concepts, Inc. Polyaxial pedicle screw having a compression locking rod gripping mechanism
US6783526B1 (en) 1997-05-15 2004-08-31 Howmedica Osteonics Corp. Transverse rod connector clip
US5891145A (en) 1997-07-14 1999-04-06 Sdgi Holdings, Inc. Multi-axial screw
US6454769B2 (en) * 1997-08-04 2002-09-24 Spinal Concepts, Inc. System and method for stabilizing the human spine with a bone plate
FR2770767B1 (en) 1997-11-10 2000-03-10 Dimso Sa Implant for vertebra
KR20010032576A (en) 1997-11-29 2001-04-25 안토니 알. 피어스 Surgical implant and surgical fixing screw
US5980523A (en) 1998-01-08 1999-11-09 Jackson; Roger Transverse connectors for spinal rods
EP0933065A1 (en) 1998-02-02 1999-08-04 Sulzer Orthopädie AG Pivotable attachment system for a bone screw
FR2774581B1 (en) 1998-02-10 2000-08-11 Dimso Sa interspinous stabilizer fix has thorny processes of two vertebrae
US6010503A (en) 1998-04-03 2000-01-04 Spinal Innovations, Llc Locking mechanism
DE69928389T2 (en) 1998-04-29 2006-06-22 Stryker Spine Spinal osteosynthesis system, in particular for front fixing
FR2778089B1 (en) 1998-04-30 2000-07-21 Dimso Sa Spinal osteosynthesis system with flange and lock
DE29808593U1 (en) 1998-05-13 1999-10-28 Howmedica Gmbh A device for connecting two spaced longitudinal rods of a spinal implant
US6113601A (en) 1998-06-12 2000-09-05 Bones Consulting, Llc Polyaxial pedicle screw having a loosely coupled locking cap
US5989251A (en) 1998-06-17 1999-11-23 Surgical Dynamics, Inc. Apparatus for spinal stabilization
US6090111A (en) 1998-06-17 2000-07-18 Surgical Dynamics, Inc. Device for securing spinal rods
US6565565B1 (en) 1998-06-17 2003-05-20 Howmedica Osteonics Corp. Device for securing spinal rods
FR2781663B1 (en) 1998-07-30 2000-10-13 Materiel Orthopedique En Abreg Device for spinal osteosynthesis
US6231575B1 (en) 1998-08-27 2001-05-15 Martin H. Krag Spinal column retainer
FR2783411B1 (en) 1998-09-18 2000-12-01 Eurosurgical Posterior spinal osteosynthesis device
US5925047A (en) 1998-10-19 1999-07-20 Third Millennium Engineering, Llc Coupled rod, anterior vertebral body screw, and staple assembly
US5899904A (en) 1998-10-19 1999-05-04 Third Milennium Engineering, Llc Compression locking vertebral body screw, staple, and rod assembly
US5947969A (en) 1998-10-19 1999-09-07 Third Millennium Engineering, Llc Rotatable locking vertebral body screw, staple and rod assembly
US5910142A (en) 1998-10-19 1999-06-08 Bones Consulting, Llc Polyaxial pedicle screw having a rod clamping split ferrule coupling element
US6033410A (en) 1999-01-04 2000-03-07 Bristol-Myers Squibb Company Orthopaedic instrumentation
US6050997A (en) 1999-01-25 2000-04-18 Mullane; Thomas S. Spinal fixation system
KR100324698B1 (en) 1999-01-30 2002-02-27 구자교 Spine fixing device
US6302888B1 (en) 1999-03-19 2001-10-16 Interpore Cross International Locking dovetail and self-limiting set screw assembly for a spinal stabilization member
DE60032225T2 (en) 1999-03-30 2007-09-13 Howmedica Osteonics Corp. Apparatus for stabilization of the spine
US6183473B1 (en) 1999-04-21 2001-02-06 Richard B Ashman Variable angle connection assembly for a spinal implant system
US6299613B1 (en) 1999-04-23 2001-10-09 Sdgi Holdings, Inc. Method for the correction of spinal deformities through vertebral body tethering without fusion
US6210413B1 (en) 1999-04-23 2001-04-03 Sdgi Holdings, Inc. Connecting apparatus using shape-memory technology
US6273888B1 (en) 1999-05-28 2001-08-14 Sdgi Holdings, Inc. Device and method for selectively preventing the locking of a shape-memory alloy coupling system
US6254602B1 (en) 1999-05-28 2001-07-03 Sdgi Holdings, Inc. Advanced coupling device using shape-memory technology
US6547789B1 (en) 1999-07-02 2003-04-15 Sulzer Orthopedics Ltd. Holding apparatus for the spinal column
FR2796546B1 (en) 1999-07-23 2001-11-30 Eurosurgical multiaxis connector for spinal implant
DE19936286C2 (en) 1999-08-02 2002-01-17 Lutz Biedermann bone screw
US7553329B2 (en) 1999-08-18 2009-06-30 Intrinsic Therapeutics, Inc. Stabilized intervertebral disc barrier
US7220281B2 (en) 1999-08-18 2007-05-22 Intrinsic Therapeutics, Inc. Implant for reinforcing and annulus fibrosis
US6280442B1 (en) 1999-09-01 2001-08-28 Sdgi Holdings, Inc. Multi-axial bone screw assembly
DE19944120B4 (en) 1999-09-15 2008-08-28 Ulrich Gmbh & Co. Kg A bone screw for variable-angle connection to a longitudinal support
CA2423973A1 (en) 1999-09-27 2001-04-05 Blackstone Medical, Inc. A surgical screw system and related methods
US6554834B1 (en) 1999-10-07 2003-04-29 Stryker Spine Slotted head pedicle screw assembly
US6217578B1 (en) 1999-10-19 2001-04-17 Stryker Spine S.A. Spinal cross connector
US6592625B2 (en) 1999-10-20 2003-07-15 Anulex Technologies, Inc. Spinal disc annulus reconstruction method and spinal disc annulus stent
US6610091B1 (en) 1999-10-22 2003-08-26 Archus Orthopedics Inc. Facet arthroplasty devices and methods
US6811567B2 (en) 1999-10-22 2004-11-02 Archus Orthopedics Inc. Facet arthroplasty devices and methods
DE10005385A1 (en) 2000-02-07 2001-08-09 Ulrich Gmbh & Co Kg pedicle screw
US6248106B1 (en) 2000-02-25 2001-06-19 Bret Ferree Cross-coupled vertebral stabilizers
US6293949B1 (en) 2000-03-01 2001-09-25 Sdgi Holdings, Inc. Superelastic spinal stabilization system and method
KR200200582Y1 (en) 2000-03-15 2000-10-16 최길운 Prosthesis for connecting bone
US6309391B1 (en) 2000-03-15 2001-10-30 Sdgi Holding, Inc. Multidirectional pivoting bone screw and fixation system
US6565566B1 (en) 2000-03-22 2003-05-20 Spinal Concepts, Inc. Sacral screw assembly and method
US6805695B2 (en) 2000-04-04 2004-10-19 Spinalabs, Llc Devices and methods for annular repair of intervertebral discs
JP2001309923A (en) 2000-04-28 2001-11-06 Robert Reed Shokai Co Ltd System supporting spinal rod and connection parts to be used therefor
US6645207B2 (en) 2000-05-08 2003-11-11 Robert A. Dixon Method and apparatus for dynamized spinal stabilization
US6749614B2 (en) 2000-06-23 2004-06-15 Vertelink Corporation Formable orthopedic fixation system with cross linking
US6482207B1 (en) 2000-07-13 2002-11-19 Fastenetix, Llc Efficient assembling modular locking pedicle screw
EP1174092A3 (en) 2000-07-22 2003-03-26 Corin Spinal Systems Limited A pedicle attachment assembly
FR2812185B1 (en) 2000-07-25 2003-02-28 Spine Next Sa Rigid connecting piece for the stabilization of the spine
US6626905B1 (en) 2000-08-02 2003-09-30 Sulzer Spine-Tech Inc. Posterior oblique lumbar arthrodesis
US6458131B1 (en) 2000-08-07 2002-10-01 Salut, Ltd. Apparatus and method for reducing spinal deformity
US20060025771A1 (en) 2000-08-23 2006-02-02 Jackson Roger P Helical reverse angle guide and advancement structure with break-off extensions
US6554831B1 (en) 2000-09-01 2003-04-29 Hopital Sainte-Justine Mobile dynamic system for treating spinal disorder
US6485491B1 (en) 2000-09-15 2002-11-26 Sdgi Holdings, Inc. Posterior fixation system
US6755829B1 (en) 2000-09-22 2004-06-29 Depuy Acromed, Inc. Lock cap anchor assembly for orthopaedic fixation
US6620164B2 (en) 2000-09-22 2003-09-16 Showa Ika Kohgyo Co., Ltd. Rod for cervical vertebra and connecting system thereof
US6695845B2 (en) 2000-10-16 2004-02-24 Robert A Dixon Method and apparatus utilizing interference fit screw shanks for nonmetallic spinal stabilization
US6520962B1 (en) 2000-10-23 2003-02-18 Sdgi Holdings, Inc. Taper-locked adjustable connector
DE10055888C1 (en) 2000-11-10 2002-04-25 Biedermann Motech Gmbh Bone screw, has connector rod receiving part with unsymmetrically arranged end bores
US6656181B2 (en) 2000-11-22 2003-12-02 Robert A Dixon Method and device utilizing tapered screw shanks for spinal stabilization
US6565605B2 (en) 2000-12-13 2003-05-20 Medicinelodge, Inc. Multiple facet joint replacement
DE50100793D1 (en) 2000-12-27 2003-11-20 Biedermann Motech Gmbh Screw for connection to a bar
JP4471491B2 (en) 2000-12-27 2010-06-02 京セラ株式会社 Vertebra correction fixation device
US6488681B2 (en) 2001-01-05 2002-12-03 Stryker Spine S.A. Pedicle screw assembly
EP1351614A2 (en) 2001-01-12 2003-10-15 DePuy Acromed, Inc. Polyaxial screw with improved locking
US6451021B1 (en) 2001-02-15 2002-09-17 Third Millennium Engineering, Llc Polyaxial pedicle screw having a rotating locking element
DE10108965B4 (en) 2001-02-17 2006-02-23 DePuy Spine Sàrl bone screw
US7104991B2 (en) 2001-02-27 2006-09-12 Robert A Dixon Method and device for using extended interference fit screw shanks for spinal stabilization
US6827743B2 (en) 2001-02-28 2004-12-07 Sdgi Holdings, Inc. Woven orthopedic implants
US6652585B2 (en) 2001-02-28 2003-11-25 Sdgi Holdings, Inc. Flexible spine stabilization system
US7090698B2 (en) 2001-03-02 2006-08-15 Facet Solutions Method and apparatus for spine joint replacement
US7344539B2 (en) 2001-03-30 2008-03-18 Depuy Acromed, Inc. Intervertebral connection system
DE10116412C1 (en) 2001-04-02 2003-01-16 Ulrich Gmbh & Co Kg Implant for insertion between vertebral bodies of the spine
US6554832B2 (en) 2001-04-02 2003-04-29 Endius Incorporated Polyaxial transverse connector
DK1252865T3 (en) 2001-04-24 2006-03-06 Co Ligne Ag Instrumentation for stabilizing certain vertebrae of the spine
US6478797B1 (en) 2001-05-16 2002-11-12 Kamaljit S. Paul Spinal fixation device
US6475219B1 (en) 2001-06-07 2002-11-05 Alexis P. Shelokov Anterior vertebral protection method and device
US20030004511A1 (en) 2001-06-27 2003-01-02 Ferree Bret A. Polyaxial pedicle screw system
FR2827498B1 (en) 2001-07-18 2004-05-14 Frederic Fortin flexible vertebral connecting device consists of elements which overcomes a deficiency of the spine
FR2827499B1 (en) 2001-07-20 2004-05-07 Henry Graf A intervertebral link
JP4755782B2 (en) 2001-08-01 2011-08-24 昭和医科工業株式会社 Implants for osteosynthesis device
FR2829014B1 (en) 2001-09-03 2005-04-08 Stryker Spine Spinal osteosynthesis system comprising a bearing block
US6899714B2 (en) 2001-10-03 2005-05-31 Vaughan Medical Technologies, Inc. Vertebral stabilization assembly and method
US6652526B1 (en) 2001-10-05 2003-11-25 Ruben P. Arafiles Spinal stabilization rod fastener
GB2382304A (en) 2001-10-10 2003-05-28 Dilip Kumar Sengupta An assembly for soft stabilisation of vertebral bodies of the spine
US6623485B2 (en) 2001-10-17 2003-09-23 Hammill Manufacturing Company Split ring bone screw for a spinal fixation system
US6887242B2 (en) 2001-10-17 2005-05-03 Ortho Innovations, Llc Split ring bone screw for a spinal fixation system
US6783527B2 (en) 2001-10-30 2004-08-31 Sdgi Holdings, Inc. Flexible spinal stabilization system and method
FR2832620B1 (en) 2001-11-27 2004-01-23 Eurosurgical Anchoring system for vertebral Connector
US6572653B1 (en) 2001-12-07 2003-06-03 Rush E. Simonson Vertebral implant adapted for posterior insertion
FR2833151B1 (en) 2001-12-12 2004-09-17 Ldr Medical Bone anchoring implant head polyaxial
FR2835173B1 (en) 2002-01-28 2004-11-05 Biomet Merck France inter-vertebral implant thorny
US6932817B2 (en) 2002-02-01 2005-08-23 Innovative Spinal Design Polyaxial modular skeletal hook
US7678136B2 (en) 2002-02-04 2010-03-16 Spinal, Llc Spinal fixation assembly
US7163538B2 (en) * 2002-02-13 2007-01-16 Cross Medical Products, Inc. Posterior rod system
FR2836368B1 (en) 2002-02-25 2005-01-14 Spine Next Sa A sequential binding
US7282064B2 (en) 2003-02-11 2007-10-16 Spinefrontier Lls Apparatus and method for connecting spinal vertebrae
DE10213855A1 (en) 2002-03-27 2003-10-16 Biedermann Motech Gmbh Bone anchoring device for stabilizing bone segments and receiving part of a bone anchoring device
US7530992B2 (en) 2002-03-27 2009-05-12 Biedermann Motech Gmbh Bone anchoring device for stabilising bone segments and seat part of a bone anchoring device
US6966910B2 (en) 2002-04-05 2005-11-22 Stephen Ritland Dynamic fixation device and method of use
US7294128B2 (en) 2002-04-09 2007-11-13 Nas Medical Technologies, Inc. Bone fixation apparatus
US6740086B2 (en) 2002-04-18 2004-05-25 Spinal Innovations, Llc Screw and rod fixation assembly and device
US7048736B2 (en) 2002-05-17 2006-05-23 Sdgi Holdings, Inc. Device for fixation of spinous processes
EP1509148B1 (en) 2002-05-21 2011-03-16 Warsaw Orthopedic, Inc. Vertebrae bone anchor and cable for coupling it to a rod
DE20207851U1 (en) 2002-05-21 2002-11-14 Metz Stavenhagen Peter Anchoring element for fastening a rod of a device for adjusting a human or animal spine to a vertebral bone
EP1364622B1 (en) 2002-05-21 2005-07-20 Spinelab GmbH Elastical system for stabilising the spine
US7060066B2 (en) 2002-06-28 2006-06-13 Mayo Foundation For Medical Education And Research Spinal fixation support device and methods of using
FR2842093B1 (en) 2002-07-12 2005-04-15 Scient X Bone anchor with spherical joint
US20040015166A1 (en) 2002-07-22 2004-01-22 Gorek Josef E. System and method for stabilizing the spine by securing spine stabilization rods in crossed disposition
FR2842724B1 (en) 2002-07-23 2005-05-27 Spine Next Sa spinal fixation system
US7107091B2 (en) 2002-07-25 2006-09-12 Orthosoft Inc. Multiple bone tracking
DE10236691B4 (en) 2002-08-09 2005-12-01 Biedermann Motech Gmbh A dynamic stabilization device for bones, in particular for vertebrae
DE10237531A1 (en) 2002-08-16 2004-02-26 Tutogen Medical Gmbh implant
US7306603B2 (en) 2002-08-21 2007-12-11 Innovative Spinal Technologies Device and method for percutaneous placement of lumbar pedicle screws and connecting rods
US6726689B2 (en) 2002-09-06 2004-04-27 Roger P. Jackson Helical interlocking mating guide and advancement structure
US20040049285A1 (en) 2002-09-09 2004-03-11 Brian Haas Duo-fixation prosthetic joints
FR2844180B1 (en) 2002-09-11 2005-08-05 Spinevision Connecting element for the dynamic stabilization of a spinal fixation system and spinal fixation system comprising such element
JP4047112B2 (en) 2002-09-12 2008-02-13 昭和医科工業株式会社 Rod fixing structure of the vertebra connection member
FR2845587B1 (en) 2002-10-14 2005-01-21 Scient X dynamic device intervertebral binding ALL TRAVEL multidirectional control
US9539012B2 (en) 2002-10-30 2017-01-10 Zimmer Spine, Inc. Spinal stabilization systems with quick-connect sleeve assemblies for use in surgical procedures
EP1558157B1 (en) 2002-10-30 2012-11-21 Zimmer Spine, Inc. Spinal stabilization system insertion
US20040147928A1 (en) 2002-10-30 2004-07-29 Landry Michael E. Spinal stabilization system using flexible members
FR2847152B1 (en) 2002-11-19 2005-02-18 Eurosurgical An anchoring vertebral and locking device on a polyaxial screw
US20040111088A1 (en) 2002-12-06 2004-06-10 Picetti George D. Multi-rod bone attachment member
FR2848408B1 (en) 2002-12-17 2005-08-19 Vitatech Device anterior plate for maintaining the spine
US7101398B2 (en) 2002-12-31 2006-09-05 Depuy Acromed, Inc. Prosthetic facet joint ligament
US6843791B2 (en) 2003-01-10 2005-01-18 Depuy Acromed, Inc. Locking cap assembly for spinal fixation instrumentation
US7104992B2 (en) 2003-01-14 2006-09-12 Ebi, L.P. Spinal fixation system
US20040158247A1 (en) 2003-02-07 2004-08-12 Arthit Sitiso Polyaxial pedicle screw system
US7875060B2 (en) 2003-09-24 2011-01-25 Spinefrontier, LLS Multi-axial screw with a spherical landing
US20040162560A1 (en) 2003-02-19 2004-08-19 Raynor Donald E. Implant device including threaded locking mechanism
EP1596738A4 (en) 2003-02-25 2010-01-20 Stephen Ritland Adjustable rod and connector device and method of use
US20060200128A1 (en) 2003-04-04 2006-09-07 Richard Mueller Bone anchor
US6964666B2 (en) 2003-04-09 2005-11-15 Jackson Roger P Polyaxial bone screw locking mechanism
US7473267B2 (en) 2003-04-25 2009-01-06 Warsaw Orthopedic, Inc. System and method for minimally invasive posterior fixation
US20050182400A1 (en) 2003-05-02 2005-08-18 Jeffrey White Spine stabilization systems, devices and methods
US7615068B2 (en) 2003-05-02 2009-11-10 Applied Spine Technologies, Inc. Mounting mechanisms for pedicle screws and related assemblies
US20060229613A1 (en) 2004-12-31 2006-10-12 Timm Jens P Sheath assembly for spinal stabilization device
US7713287B2 (en) 2003-05-02 2010-05-11 Applied Spine Technologies, Inc. Dynamic spine stabilizer
ES2387420T3 (en) 2003-05-02 2012-09-21 Yale University dynamic spine stabilizer
US8652175B2 (en) 2003-05-02 2014-02-18 Rachiotek, Llc Surgical implant devices and systems including a sheath member
US20050182401A1 (en) 2003-05-02 2005-08-18 Timm Jens P. Systems and methods for spine stabilization including a dynamic junction
US20050177164A1 (en) 2003-05-02 2005-08-11 Carmen Walters Pedicle screw devices, systems and methods having a preloaded set screw
US6951561B2 (en) 2003-05-06 2005-10-04 Triage Medical, Inc. Spinal stabilization device
DE10320417A1 (en) 2003-05-07 2004-12-02 Biedermann Motech Gmbh Dynamic anchoring device and dynamic stabilization device for bones, in particular for vertebrae, with such an anchoring device
US20040230304A1 (en) 2003-05-14 2004-11-18 Archus Orthopedics Inc. Prostheses, tools and methods for replacement of natural facet joints with artifical facet joint surfaces
US7377923B2 (en) 2003-05-22 2008-05-27 Alphatec Spine, Inc. Variable angle spinal screw assembly
US6986771B2 (en) 2003-05-23 2006-01-17 Globus Medical, Inc. Spine stabilization system
FR2855392B1 (en) 2003-05-28 2005-08-05 Spinevision Connection device for osteosynthesis spinal
US7270665B2 (en) 2003-06-11 2007-09-18 Sdgi Holdings, Inc. Variable offset spinal fixation system
US6716214B1 (en) 2003-06-18 2004-04-06 Roger P. Jackson Polyaxial bone screw with spline capture connection
US8366753B2 (en) 2003-06-18 2013-02-05 Jackson Roger P Polyaxial bone screw assembly with fixed retaining structure
US7087057B2 (en) 2003-06-27 2006-08-08 Depuy Acromed, Inc. Polyaxial bone screw
US7309355B2 (en) 2003-06-27 2007-12-18 Depuy Mitek, Inc. Flexible tibial sheath
US7731734B2 (en) 2003-06-27 2010-06-08 Medicrea Technologies Vertebral osteosynthesis equipment
US6945974B2 (en) 2003-07-07 2005-09-20 Aesculap Inc. Spinal stabilization implant and method of application
US8137386B2 (en) 2003-08-28 2012-03-20 Jackson Roger P Polyaxial bone screw apparatus
US7763052B2 (en) 2003-12-05 2010-07-27 N Spine, Inc. Method and apparatus for flexible fixation of a spine
US7815665B2 (en) 2003-09-24 2010-10-19 N Spine, Inc. Adjustable spinal stabilization system
US8979900B2 (en) 2003-09-24 2015-03-17 DePuy Synthes Products, LLC Spinal stabilization device
US7137985B2 (en) 2003-09-24 2006-11-21 N Spine, Inc. Marking and guidance method and system for flexible fixation of a spine
US20050203513A1 (en) 2003-09-24 2005-09-15 Tae-Ahn Jahng Spinal stabilization device
US7335201B2 (en) 2003-09-26 2008-02-26 Zimmer Spine, Inc. Polyaxial bone screw with torqueless fastening
FR2860138A1 (en) 2003-09-26 2005-04-01 Stryker Spine Assembly and bone fixation METHOD
US20050113923A1 (en) 2003-10-03 2005-05-26 David Acker Prosthetic spinal disc nucleus
US20050080415A1 (en) 2003-10-14 2005-04-14 Keyer Thomas R. Polyaxial bone anchor and method of spinal fixation
US7588588B2 (en) 2003-10-21 2009-09-15 Innovative Spinal Technologies System and method for stabilizing of internal structures
US7967826B2 (en) 2003-10-21 2011-06-28 Theken Spine, Llc Connector transfer tool for internal structure stabilization systems
US7905907B2 (en) 2003-10-21 2011-03-15 Theken Spine, Llc Internal structure stabilization system for spanning three or more structures
WO2005041793A3 (en) 2003-10-23 2005-11-10 Steven D Ainsworth Spinal mobility preservation apparatus and method
US20050090822A1 (en) 2003-10-24 2005-04-28 Dipoto Gene Methods and apparatus for stabilizing the spine through an access device
US20050096652A1 (en) 2003-10-31 2005-05-05 Burton Charles V. Integral flexible spine stabilization device and method
DE50304374D1 (en) 2003-10-31 2006-09-07 Spinelab Ag Closure device for pedicle screws for fixation of elastic rod elements
EP1578314B1 (en) 2003-11-07 2007-05-30 Impliant Ltd. Spinal prostheses
US7083622B2 (en) 2003-11-10 2006-08-01 Simonson Peter M Artificial facet joint and method
US8562649B2 (en) 2004-02-17 2013-10-22 Gmedelaware 2 Llc System and method for multiple level facet joint arthroplasty and fusion
US7553320B2 (en) 2003-12-10 2009-06-30 Warsaw Orthopedic, Inc. Method and apparatus for replacing the function of facet joints
US7806914B2 (en) 2003-12-31 2010-10-05 Spine Wave, Inc. Dynamic spinal stabilization system
US7678137B2 (en) 2004-01-13 2010-03-16 Life Spine, Inc. Pedicle screw constructs for spine fixation systems
US7862587B2 (en) 2004-02-27 2011-01-04 Jackson Roger P Dynamic stabilization assemblies, tool set and method
US7819902B2 (en) 2004-02-27 2010-10-26 Custom Spine, Inc. Medialised rod pedicle screw assembly
US7862594B2 (en) 2004-02-27 2011-01-04 Custom Spine, Inc. Polyaxial pedicle screw assembly
DE102004010844A1 (en) 2004-03-05 2005-10-06 Biedermann Motech Gmbh Stabilization device for dynamic stabilization of vertebrae or bones and rod-shaped element for such a stabilization device
US7214227B2 (en) 2004-03-22 2007-05-08 Innovative Spinal Technologies Closure member for a medical implant device
US7717939B2 (en) 2004-03-31 2010-05-18 Depuy Spine, Inc. Rod attachment for head to head cross connector
US8475495B2 (en) 2004-04-08 2013-07-02 Globus Medical Polyaxial screw
US7503924B2 (en) 2004-04-08 2009-03-17 Globus Medical, Inc. Polyaxial screw
US20050228382A1 (en) 2004-04-12 2005-10-13 Marc Richelsoph Screw and rod fixation assembly and device
US7648520B2 (en) 2004-04-16 2010-01-19 Kyphon Sarl Pedicle screw assembly
US7833256B2 (en) 2004-04-16 2010-11-16 Biedermann Motech Gmbh Elastic element for the use in a stabilization device for bones and vertebrae and method for the manufacture of such elastic element
US7674293B2 (en) 2004-04-22 2010-03-09 Facet Solutions, Inc. Crossbar spinal prosthesis having a modular design and related implantation methods
US8187303B2 (en) 2004-04-22 2012-05-29 Gmedelaware 2 Llc Anti-rotation fixation element for spinal prostheses
US7051451B2 (en) 2004-04-22 2006-05-30 Archus Orthopedics, Inc. Facet joint prosthesis measurement and implant tools
US20050261770A1 (en) 2004-04-22 2005-11-24 Kuiper Mark K Crossbar spinal prosthesis having a modular design and related implantation methods
US20050267470A1 (en) 2004-05-13 2005-12-01 Mcbride Duncan Q Spinal stabilization system to flexibly connect vertebrae
FR2870711B1 (en) 2004-05-26 2006-09-01 Sdgi Holdings Inc Device connecting the rod of a spinal osteosynthesis device to a vertebra, and the osteosynthesis device comprising
US7935135B2 (en) 2004-06-09 2011-05-03 Zimmer Spine, Inc. Spinal fixation device
US7559943B2 (en) 2004-06-09 2009-07-14 Zimmer Spine, Inc. Spinal fixation device with internal drive structure
US8858599B2 (en) 2004-06-09 2014-10-14 Warsaw Orthopedic, Inc. Systems and methods for flexible spinal stabilization
US7857834B2 (en) 2004-06-14 2010-12-28 Zimmer Spine, Inc. Spinal implant fixation assembly
US7731736B2 (en) 2004-06-14 2010-06-08 Zimmer Spine, Inc. Fastening system for spinal stabilization system
US20060247631A1 (en) 2005-04-27 2006-11-02 Ahn Sae Y Spinal pedicle screw assembly
US7871413B2 (en) 2004-07-21 2011-01-18 Solco Biomedical Co., Ltd. Pedicle screw and operating device thereof
US7658753B2 (en) 2004-08-03 2010-02-09 K Spine, Inc. Device and method for correcting a spinal deformity
WO2006017641A3 (en) 2004-08-03 2009-04-09 Vertech Innovations L L C Spinous process reinforcement device and method
US7854752B2 (en) 2004-08-09 2010-12-21 Theken Spine, Llc System and method for dynamic skeletal stabilization
US7766945B2 (en) 2004-08-10 2010-08-03 Lanx, Inc. Screw and rod fixation system
WO2006016371A3 (en) 2004-08-13 2006-05-04 Mazor Surgical Tech Ltd Minimally invasive spinal fusion
US20060052784A1 (en) 2004-08-17 2006-03-09 Zimmer Spine, Inc. Polyaxial device for spine stabilization during osteosynthesis
US20060052783A1 (en) 2004-08-17 2006-03-09 Dant Jack A Polyaxial device for spine stabilization during osteosynthesis
US20060058787A1 (en) 2004-08-24 2006-03-16 Stryker Spine Spinal implant assembly
US20060058788A1 (en) 2004-08-27 2006-03-16 Hammer Michael A Multi-axial connection system
US20060084978A1 (en) 2004-09-30 2006-04-20 Mokhtar Mourad B Spinal fixation system and method
US8092496B2 (en) 2004-09-30 2012-01-10 Depuy Spine, Inc. Methods and devices for posterior stabilization
US20060129148A1 (en) 2004-10-01 2006-06-15 Simmons Edward D Screw sleeve made of polyetheretherketone (PEEK) for augmentation of bone screw insertion in osteoporotic or revision lumbar spine instrumentation
US7722654B2 (en) 2004-10-05 2010-05-25 Warsaw Orthopedic, Inc. Spinal implants with multi-axial anchor assembly and methods
US7572280B2 (en) 2004-10-05 2009-08-11 Warsaw Orthopedic, Inc. Multi-axial anchor assemblies for spinal implants and methods
US7794477B2 (en) 2004-10-05 2010-09-14 Warsaw Orthopedic, Inc. Spinal implants and methods with extended multi-axial anchor assemblies
US8012207B2 (en) 2004-10-20 2011-09-06 Vertiflex, Inc. Systems and methods for posterior dynamic stabilization of the spine
US8123807B2 (en) 2004-10-20 2012-02-28 Vertiflex, Inc. Systems and methods for posterior dynamic stabilization of the spine
US8162985B2 (en) 2004-10-20 2012-04-24 The Board Of Trustees Of The Leland Stanford Junior University Systems and methods for posterior dynamic stabilization of the spine
US8409282B2 (en) 2004-10-20 2013-04-02 Vertiflex, Inc. Systems and methods for posterior dynamic stabilization of the spine
US20080262554A1 (en) 2004-10-20 2008-10-23 Stanley Kyle Hayes Dyanamic rod
US8167944B2 (en) 2004-10-20 2012-05-01 The Board Of Trustees Of The Leland Stanford Junior University Systems and methods for posterior dynamic stabilization of the spine
US9023084B2 (en) 2004-10-20 2015-05-05 The Board Of Trustees Of The Leland Stanford Junior University Systems and methods for stabilizing the motion or adjusting the position of the spine
US8317864B2 (en) 2004-10-20 2012-11-27 The Board Of Trustees Of The Leland Stanford Junior University Systems and methods for posterior dynamic stabilization of the spine
KR20070084138A (en) 2004-10-25 2007-08-24 알파스파인, 아이엔씨. Pedicle screw systems and methods of assembling/installing the same
WO2006047707A3 (en) 2004-10-25 2006-06-22 Alphaspine Inc Pedicle screw systems and methods of assembling/installing the same
US7691129B2 (en) 2004-10-27 2010-04-06 Felix Brent A Spinal stabilizing system
US7513905B2 (en) 2004-11-03 2009-04-07 Jackson Roger P Polyaxial bone screw
US20060095035A1 (en) 2004-11-03 2006-05-04 Jones Robert J Instruments and methods for reduction of vertebral bodies
US7572279B2 (en) 2004-11-10 2009-08-11 Jackson Roger P Polyaxial bone screw with discontinuous helically wound capture connection
US7833250B2 (en) 2004-11-10 2010-11-16 Jackson Roger P Polyaxial bone screw with helically wound capture connection
US7625396B2 (en) 2004-11-23 2009-12-01 Jackson Roger P Polyaxial bone screw with multi-part shank retainer
US8152810B2 (en) 2004-11-23 2012-04-10 Jackson Roger P Spinal fixation tool set and method
JP2008521563A (en) 2004-12-01 2008-06-26 ザ リージェンツ オブ ザ ユニヴァーシティ オブ ザ カリフォルニア Intervertebral diseases processing system, apparatus and method
US7811288B2 (en) 2004-12-02 2010-10-12 Zimmer Spine, Inc. Instruments and methods for adjusting separation distance of vertebral bodies with a minimally invasive spinal stabilization procedure
US7578833B2 (en) 2004-12-13 2009-08-25 Dr. Robert S. Bray, Jr. Bone fastener assembly for bone retention apparatus
US8066749B2 (en) 2004-12-13 2011-11-29 Warsaw Orthopedic, Inc. Implant for stabilizing a bone graft during spinal fusion
US7306606B2 (en) 2004-12-15 2007-12-11 Orthopaedic Innovations, Inc. Multi-axial bone screw mechanism
EP1719468A1 (en) 2004-12-17 2006-11-08 Zimmer GmbH Intervertebral stabilization system
US20060149242A1 (en) 2004-12-17 2006-07-06 Gary Kraus Spinal stabilization systems supplemented with diagnostically opaque materials
US7811311B2 (en) 2004-12-30 2010-10-12 Warsaw Orthopedic, Inc. Screw with deployable interlaced dual rods
FR2880256B1 (en) 2004-12-30 2007-04-06 Neuro France Implants Sarl of spinal osteosynthesis system
US7815664B2 (en) 2005-01-04 2010-10-19 Warsaw Orthopedic, Inc. Systems and methods for spinal stabilization with flexible elements
US7445627B2 (en) 2005-01-31 2008-11-04 Alpinespine, Llc Polyaxial pedicle screw assembly
US20070088359A1 (en) 2005-02-07 2007-04-19 Woods Richard W Universal dynamic spine stabilization device and method of use
US7294129B2 (en) 2005-02-18 2007-11-13 Ebi, L.P. Spinal fixation device and associated method
WO2006089292A3 (en) 2005-02-18 2007-12-06 M S Abdou Devices and methods for dynamic fixation of skeletal structure
US7604654B2 (en) 2005-02-22 2009-10-20 Stryker Spine Apparatus and method for dynamic vertebral stabilization
US7789896B2 (en) 2005-02-22 2010-09-07 Jackson Roger P Polyaxial bone screw assembly
US8167913B2 (en) 2005-03-03 2012-05-01 Altus Partners, Llc Spinal stabilization using bone anchor and anchor seat with tangential locking feature
WO2006096381A3 (en) 2005-03-03 2007-02-22 Accin Corp Spinal stabilization using bone anchor seat and cross coupling with improved locking feature
US7951172B2 (en) 2005-03-04 2011-05-31 Depuy Spine Sarl Constrained motion bone screw assembly
US20060229607A1 (en) 2005-03-16 2006-10-12 Sdgi Holdings, Inc. Systems, kits and methods for treatment of the spinal column using elongate support members
US7338491B2 (en) 2005-03-22 2008-03-04 Spinefrontier Inc Spinal fixation locking mechanism
US20060235385A1 (en) 2005-03-31 2006-10-19 Dale Whipple Low profile polyaxial screw
US20060241757A1 (en) 2005-03-31 2006-10-26 Sdgi Holdings, Inc. Intervertebral prosthetic device for spinal stabilization and method of manufacturing same
WO2006105935A1 (en) 2005-04-04 2006-10-12 Zimmer Gmbh Pedicle screw
US7708762B2 (en) 2005-04-08 2010-05-04 Warsaw Orthopedic, Inc. Systems, devices and methods for stabilization of the spinal column
EP1871253B1 (en) 2005-04-08 2015-09-16 Paradigm Spine, LLC Interspinous vertebral and lumbosacral stabilization devices
US7794481B2 (en) 2005-04-22 2010-09-14 Warsaw Orthopedic, Inc. Force limiting coupling assemblies for spinal implants
US7585312B2 (en) 2005-04-29 2009-09-08 Warsaw Orthopedic, Inc. Spinal stabilization apparatus and method
US20060247623A1 (en) 2005-04-29 2006-11-02 Sdgi Holdings, Inc. Local delivery of an active agent from an orthopedic implant
US7850715B2 (en) 2005-04-29 2010-12-14 Warsaw Orthopedic Inc. Orthopedic implant apparatus
US20060264937A1 (en) 2005-05-04 2006-11-23 White Patrick M Mobile spine stabilization device
US20060264935A1 (en) 2005-05-04 2006-11-23 White Patrick M Orthopedic stabilization device
US7828830B2 (en) 2005-05-12 2010-11-09 Lanx, Inc. Dynamic spinal stabilization
US7658752B2 (en) 2005-06-10 2010-02-09 DePay Spine, Inc. Posterior dynamic stabilization x-device
US7828825B2 (en) 2005-06-20 2010-11-09 Warsaw Orthopedic, Inc. Multi-level multi-functional spinal stabilization systems and methods
US7799060B2 (en) 2005-06-20 2010-09-21 Warsaw Orthopedic, Inc. Multi-directional spinal stabilization systems and methods
US20070016190A1 (en) 2005-07-14 2007-01-18 Medical Device Concepts Llc Dynamic spinal stabilization system
US7811309B2 (en) 2005-07-26 2010-10-12 Applied Spine Technologies, Inc. Dynamic spine stabilization device with travel-limiting functionality
US7713288B2 (en) 2005-08-03 2010-05-11 Applied Spine Technologies, Inc. Spring junction and assembly methods for spinal device
US7625394B2 (en) 2005-08-05 2009-12-01 Warsaw Orthopedic, Inc. Coupling assemblies for spinal implants
US7533672B2 (en) 2005-09-06 2009-05-19 Synthes Usa, Llc Methods and apparatus for vascular protection in spinal surgery
DE502006002049D1 (en) 2005-09-13 2008-12-24 Bird Biedermann Ag Dynamic clamping device for spinal implant
US20070083200A1 (en) 2005-09-23 2007-04-12 Gittings Darin C Spinal stabilization systems and methods
US7879074B2 (en) 2005-09-27 2011-02-01 Depuy Spine, Inc. Posterior dynamic stabilization systems and methods
KR20080068674A (en) 2005-09-30 2008-07-23 패러다임 스파인, 엘엘씨 Hinged polyaxial screw and methods of use
WO2007044836A3 (en) 2005-10-06 2007-11-29 M Samy Abdou Devices and methods for inter-vertebral orthopedic device placement
US7927359B2 (en) 2005-10-06 2011-04-19 Paradigm Spine, Llc Polyaxial screw
US20070093814A1 (en) 2005-10-11 2007-04-26 Callahan Ronald Ii Dynamic spinal stabilization systems
US8075599B2 (en) 2005-10-18 2011-12-13 Warsaw Orthopedic, Inc. Adjustable bone anchor assembly
US7862591B2 (en) 2005-11-10 2011-01-04 Warsaw Orthopedic, Inc. Intervertebral prosthetic device for spinal stabilization and method of implanting same
US7699873B2 (en) 2005-11-23 2010-04-20 Warsaw Orthopedic, Inc. Spinous process anchoring systems and methods
JP2009517174A (en) 2005-12-01 2009-04-30 ウォーソー・オーソペディック・インコーポレーテッド Side-mounted adjustable bone anchor
US7819899B2 (en) 2006-01-03 2010-10-26 Zimmer Spine, Inc. Instrument for pedicle screw adhesive materials
US7918792B2 (en) 2006-01-04 2011-04-05 Depuy Spine, Inc. Surgical retractor for use with minimally invasive spinal stabilization systems and methods of minimally invasive surgery
US7520879B2 (en) 2006-02-07 2009-04-21 Warsaw Orthopedic, Inc. Surgical instruments and techniques for percutaneous placement of spinal stabilization elements
US8029545B2 (en) 2006-02-07 2011-10-04 Warsaw Orthopedic Inc. Articulating connecting member and anchor systems for spinal stabilization
US20070233068A1 (en) 2006-02-22 2007-10-04 Sdgi Holdings, Inc. Intervertebral prosthetic assembly for spinal stabilization and method of implanting same
US20070233091A1 (en) 2006-02-23 2007-10-04 Naifeh Bill R Multi-level spherical linkage implant system
US20070233090A1 (en) 2006-02-23 2007-10-04 Naifeh Bill R Aligning cross-connector
US8262696B2 (en) 2006-02-24 2012-09-11 Medical Design, LLC Multilevel facet/laminar fixation system
US8088148B2 (en) 2006-02-24 2012-01-03 Medical Design, LLC Dynamic/static facet fixation device and method
US8470008B2 (en) 2006-03-01 2013-06-25 Warsaw Othropedic, Inc. Modular fastener assemblies for spinal stabilization systems and methods
US7927358B2 (en) 2006-03-07 2011-04-19 Zimmer Spine, Inc. Spinal stabilization device
US7842072B2 (en) 2006-03-16 2010-11-30 Zimmer Spine, Inc. Spinal fixation device with variable stiffness
US8025681B2 (en) 2006-03-29 2011-09-27 Theken Spine, Llc Dynamic motion spinal stabilization system
US7699875B2 (en) 2006-04-17 2010-04-20 Applied Spine Technologies, Inc. Spinal stabilization device with weld cap
US20070288012A1 (en) 2006-04-21 2007-12-13 Dennis Colleran Dynamic motion spinal stabilization system and device
US8435267B2 (en) 2006-04-24 2013-05-07 Spinefrontier Inc Spine fixation method and apparatus
US7563274B2 (en) 2006-04-25 2009-07-21 Warsaw Orthopedic, Inc. Surgical instruments and techniques for controlling spinal motion segments with positioning of spinal stabilization elements
US8012179B2 (en) 2006-05-08 2011-09-06 Warsaw Orthopedic, Inc. Dynamic spinal stabilization members and methods
US20070270838A1 (en) 2006-05-08 2007-11-22 Sdgi Holdings, Inc. Dynamic spinal stabilization device with dampener
US7785350B2 (en) 2006-05-08 2010-08-31 Warsaw Orthopedic, Inc. Load bearing flexible spinal connecting element
US20070288009A1 (en) 2006-06-08 2007-12-13 Steven Brown Dynamic spinal stabilization device
US7927356B2 (en) 2006-07-07 2011-04-19 Warsaw Orthopedic, Inc. Dynamic constructs for spinal stabilization
US7967847B2 (en) 2006-07-24 2011-06-28 Warsaw Orthopedic, Inc. Spinal stabilization and reconstruction with fusion rods
US20080033433A1 (en) 2006-08-01 2008-02-07 Dante Implicito Dynamic spinal stabilization device
US7806913B2 (en) 2006-08-16 2010-10-05 Depuy Spine, Inc. Modular multi-level spine stabilization system and method
US9526525B2 (en) 2006-08-22 2016-12-27 Neuropro Technologies, Inc. Percutaneous system for dynamic spinal stabilization
US20080065073A1 (en) 2006-09-08 2008-03-13 Michael Perriello Offset dynamic motion spinal stabilization system
US8425601B2 (en) 2006-09-11 2013-04-23 Warsaw Orthopedic, Inc. Spinal stabilization devices and methods of use
US20080071273A1 (en) 2006-09-15 2008-03-20 Hawkes David T Dynamic Pedicle Screw System
KR20090097909A (en) 2006-12-10 2009-09-16 패러다임 스파인, 엘엘씨 Posterior functionally dynamic stabilization system
US7828824B2 (en) 2006-12-15 2010-11-09 Depuy Spine, Inc. Facet joint prosthesis
US7875059B2 (en) 2007-01-18 2011-01-25 Warsaw Orthopedic, Inc. Variable stiffness support members
WO2008098206A1 (en) 2007-02-09 2008-08-14 Altiva Corporation Dynamic stabilization device
WO2008121343A1 (en) 2007-03-30 2008-10-09 Vertiflex, Inc. Multi-level minimally invasive spinal stabilization system
US8021396B2 (en) * 2007-06-05 2011-09-20 Spartek Medical, Inc. Configurable dynamic spinal rod and method for dynamic stabilization of the spine

Patent Citations (16)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4566677A (en) * 1982-06-11 1986-01-28 Vibrachoc Vibration damper and in particular frequency adapter for a helicopter blade
US5129899A (en) * 1991-03-27 1992-07-14 Smith & Nephew Richards Inc. Bone fixation apparatus
US5569246A (en) * 1993-12-28 1996-10-29 Asahi Kogaku Kogyo Kabushiki Kaisha Fixing instrument for spinal fusion members
US20050171543A1 (en) * 2003-05-02 2005-08-04 Timm Jens P. Spine stabilization systems and associated devices, assemblies and methods
US20050113927A1 (en) * 2003-11-25 2005-05-26 Malek Michel H. Spinal stabilization systems
US20050131406A1 (en) * 2003-12-15 2005-06-16 Archus Orthopedics, Inc. Polyaxial adjustment of facet joint prostheses
US20050143737A1 (en) * 2003-12-31 2005-06-30 John Pafford Dynamic spinal stabilization system
US7744635B2 (en) * 2004-06-09 2010-06-29 Spinal Generations, Llc Spinal fixation system
US20060052786A1 (en) * 2004-08-17 2006-03-09 Zimmer Spine, Inc. Polyaxial device for spine stabilization during osteosynthesis
US20090016808A1 (en) * 2004-09-03 2009-01-15 Oshkosh Truck Corporation Joint
US20060149234A1 (en) * 2004-12-22 2006-07-06 Stryker Spine Variable offset connectors and bone fixation methods
US20070093817A1 (en) * 2005-09-29 2007-04-26 Michael Barrus Spinal fixation system having locking and unlocking devices for use with a multi-planar, taper lock screw
US7963978B2 (en) * 2007-06-05 2011-06-21 Spartek Medical, Inc. Method for implanting a deflection rod system and customizing the deflection rod system for a particular patient need for dynamic stabilization and motion preservation spinal implantation system
US8313515B2 (en) * 2007-06-15 2012-11-20 Rachiotek, Llc Multi-level spinal stabilization system
US20090171395A1 (en) * 2007-12-28 2009-07-02 Jeon Dong M Dynamic spinal rod system
US8057517B2 (en) * 2008-02-26 2011-11-15 Spartek Medical, Inc. Load-sharing component having a deflectable post and centering spring and method for dynamic stabilization of the spine

Cited By (24)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8920453B2 (en) * 2008-06-24 2014-12-30 Extremity Medical, Llc Fixation system, an intramedullary fixation assembly and method of use
US8920476B2 (en) * 2008-06-24 2014-12-30 Extremity Medical, Llc Fixation system, an intramedullary fixation assembly and method of use
US20130053848A1 (en) * 2008-06-24 2013-02-28 Extremity Medical, Llc Fixation system, an intramedullary fixation assembly and method of use
US20130172889A1 (en) * 2008-06-24 2013-07-04 Extremity Medical, Llc Fixation system, an intramedullary fixation assembly and method of use
US20120029570A1 (en) * 2010-07-29 2012-02-02 Clariance Facet arthroplasty device
US9289244B2 (en) 2011-03-09 2016-03-22 Zimmer Spine, Inc. Polyaxial pedicle screw with increased angulation
US9532810B2 (en) * 2011-03-09 2017-01-03 Zimmer Spine, Inc. Polyaxial pedicle screw with increased angulation
US20130013004A1 (en) * 2011-03-09 2013-01-10 Zimmer Spine, Inc. Polyaxial pedicle screw with increased angulation
US8685064B2 (en) * 2011-03-09 2014-04-01 Zimmer Spine, Inc. Polyaxial pedicle screw with increased angulation
US20130085534A1 (en) * 2011-09-30 2013-04-04 Nicolas Hainard Connectors for a secondary bone anchor
US10016227B2 (en) 2011-12-08 2018-07-10 Spine Wave, Inc. Methods for percutaneously extending an existing spinal construct
US8663281B2 (en) 2011-12-08 2014-03-04 Spine Wave, Inc. Apparatus and instruments for percutaneously extending an existing spinal construct
US9629668B2 (en) 2011-12-08 2017-04-25 Spine Wave, Inc. Apparatus and devices for percutaneously extending an existing spinal construct
US8641739B2 (en) 2011-12-08 2014-02-04 Spine Wave, Inc. Methods for percutaneously extending an existing spinal construct
US8740950B2 (en) 2011-12-08 2014-06-03 Spine Wave, Inc. Methods for percutaneously attaching a cross connector to contralateral spinal constructs
US9642655B2 (en) 2011-12-08 2017-05-09 Spine Wave, Inc. Methods for percutaneously extending an existing spinal construct
US8562654B2 (en) 2011-12-08 2013-10-22 Spine Wave, Inc. Methods for percutaneously extending an existing spinal construct
US9149302B2 (en) 2011-12-08 2015-10-06 Spine Wave, Inc. Apparatus and devices for percutaneously extending an existing spinal construct
US8523906B2 (en) 2011-12-08 2013-09-03 Spine Wave, Inc. Apparatus and devices for percutaneously extending an existing spinal construct
US8337532B1 (en) * 2011-12-08 2012-12-25 Spine Wave, Inc. Methods for percutaneously extending an existing spinal construct
US20130345755A1 (en) * 2012-06-21 2013-12-26 Aesculap Implant Systems, Llc Low profile bone stabilization systems
US9510866B2 (en) * 2012-08-15 2016-12-06 Blackstone Medical, Inc. Pivoting spinal fixation devices
US20140052189A1 (en) * 2012-08-15 2014-02-20 Blackstone Medical, Inc. Pivoting spinal fixation devices
US20140074169A1 (en) * 2012-09-13 2014-03-13 Warsaw Orthopedic, Inc. Spinal correction system and method

Also Published As

Publication number Publication date Type
US20110307015A1 (en) 2011-12-15 application
US20110307013A1 (en) 2011-12-15 application
US8518085B2 (en) 2013-08-27 grant
WO2011156236A3 (en) 2012-04-19 application
WO2011156236A2 (en) 2011-12-15 application

Similar Documents

Publication Publication Date Title
US7635379B2 (en) Pedicle screw assembly with bearing surfaces
US6287311B1 (en) Multi-angle bone screw assembly using shape-memory technology
US7766915B2 (en) Dynamic fixation assemblies with inner core and outer coil-like member
US7896902B2 (en) Multi-axial double locking bone screw assembly
US8066739B2 (en) Tool system for dynamic spinal implants
US8128659B2 (en) Spinous process stabilization device and method
US7686835B2 (en) Pedicle screw system with provisional locking aspects
US7270665B2 (en) Variable offset spinal fixation system
US20070088357A1 (en) Adjustable bone anchor assembly
US7445627B2 (en) Polyaxial pedicle screw assembly
USRE39035E1 (en) Universal coupler for spinal fixation
US20050177164A1 (en) Pedicle screw devices, systems and methods having a preloaded set screw
US20050177166A1 (en) Mounting mechanisms for pedicle screws and related assemblies
US7604655B2 (en) Bone fixation system and method for using the same
US20060235389A1 (en) Spinal stabilization using bone anchor and anchor seat with tangential locking feature
US20080183215A1 (en) Multi-level minimally invasive spinal stabilization system
US8075603B2 (en) Locking polyaxial ball and socket fastener
US20090118772A1 (en) Polyaxial bone anchor with increased angulation
US20080097441A1 (en) Systems and methods for posterior dynamic stabilization of the spine
US20100114180A1 (en) Multi-planar, taper lock screw with additional lock
US20100211105A1 (en) Telescopic Rod For Posterior Dynamic Stabilization
US20060089645A1 (en) Internal fixation system for spine surgery
US20060235385A1 (en) Low profile polyaxial screw
US20080015576A1 (en) Large diameter bone anchor assembly
US20100125302A1 (en) Locking Polyaxial Ball And Socket Fastener

Legal Events

Date Code Title Description
AS Assignment

Owner name: SPARTEK MEDICAL, INC., CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:ZUCHERMAN, JAMES F.;WINSLOW, CHARLES J.;HSU, KEN Y.;AND OTHERS;SIGNING DATES FROM 20110201 TO 20110205;REEL/FRAME:025835/0202